Systems and methods for direct current nerve conduction block

ABSTRACT

Disclosed herein are systems and methods for nerve conduction block. The systems and methods can utilize at least one renewable electrode. The methods can include delivering a first direct current with a first polarity to an electrode proximate nervous tissue sufficient to block conduction in the nervous tissue. Delivering the first direct current can place the nervous tissue in a hypersuppressed state at least partially preventing conduction of the nervous tissue after cessation of delivering of the first direct current. The nervous tissue can be maintained in the hypersuppressed state for a desired period, such as at least about 1 minute.

INCORPORATION BY REFERENCE

This application is a continuation of U.S. patent application Ser. No.15/943,601, filed Apr. 2, 2018, which claims the benefit under 35 U.S.C.§ 119(e) as a nonprovisional application of U.S. Prov. App. Nos.62/481,092 filed on Apr. 3, 2017, and 62/485,882 filed on Apr. 14, 2017,each of which are incorporated by reference in their entireties. Any andall applications for which a foreign or domestic priority claim isidentified in the Application Data Sheet as filed with the presentapplication, as well as applications mentioned in the specification arehereby incorporated by reference under 37 CFR 1.57.

BACKGROUND Field of the Invention

This application relates, in some embodiments, to facilitating block ofbiological signals through nerve tissue.

The gate control theory of pain was developed in the 1960s and led tothe advent of stimulation-based pain management therapies to reduce paininputs from reaching the brain by selectively stimulatingnon-nociceptive fibers (non-pain transmitting fibers) in the spinal cordto inhibit transmission of pain stimuli to the brain (See Mendell,Constructing and Deconstructing the Gate Theory of Pain, Pain, 2014February 155(2): 210-216). Current stimulation systems for spinal cordstimulation (SCS), which act on this gate control theory to indirectlyreduce pain, typically have relied on stimulation signals in the <100 Hzfrequency range, and recently in the kHz frequency range. Stimulation ofthe dorsal root ganglia, DRG, in a similar frequency range has also beenemployed to reduce segmental pain through the same mechanism.

However, technologies based on this premise are not perfect as paintransmission inhibition is not complete and side effects such asparesthesia can be uncomfortable for patients. Therefore, it isdesirable to have systems and methods of treating pain which directlyblock pain fibers from transmitting pain signals, rather than indirectlyreducing pain signals through gate-theory activation of non-nociceptivefibers. Furthermore, block of neural tissue or neural activity has beenimplicated in not only affecting pain but also in the management ofmovement disorders, psychiatric disorders, cardiovascular health, aswell as management of disease states such as diabetes.

SUMMARY

In some embodiments, a system to modulate the action potentialtransmission along a nerve body includes an electron to ion currentconversion cell (EICCC) which comprises an electrode at which anelectrochemical process occurs to generate current in the form of ionsto change the electrical potential around the nerve and modulate thenerve membrane potential.

In some embodiments, a system to modulate the action potentialtransmission along a nerve body includes an electron to ion currentconversion cell which comprises an electrode at which a capacitivecharging process occurs to generate current in the form of ions tochange the charge density around the nerve and modulate the nervemembrane potential.

In some embodiments, a system to modulate the stimulus transmissionalong a nerve body includes an electron to ion current conversion cellwhich comprises an electrode at which an electrochemical process occursto generate current in the form of ions to change the charge densityaround the nerve and modulate the nerve membrane potential.

In some embodiments, a system to modulate the stimulus transmissionalong a nerve body includes an electron to ion current conversion cellwhich comprises an electrode at which an electrochemical process andcapacitive charging process occur to generate current in the form ofions to change the charge density around the nerve and modulate thenerve membrane potential.

In some embodiments, the system modulates the electrical potential nearthe nerve to put the nerve tissue in a blocked state.

In some embodiments, the system puts the target nerve(s) in a state ofacute nerve block.

In some embodiments, the system puts the target nerve(s) in a state ofchronic nerve block.

In some embodiments, the system modulates the electrical potential toput the nerve tissue into a suppressed state.

In some embodiments, the system puts the target nerve(s) in a state ofacute nerve suppression.

In some embodiments, the system puts the target nerve(s) in a state ofnerve hypersuppression.

In some embodiments, the electrode comprises an electrode material ofsilver, silver-chloride (Ag/AgCl).

In some embodiments, the electrode comprises an electrode material ofsilver (Ag).

In some embodiments, the electrode comprises an electrode material ofsilver-chloride (AgCl).

In some embodiments, the masses of the electrode constituent materialsare maintained in a specified range.

In some embodiments, the electrochemical processes which occur at theelectrode are reversible.

In some embodiments, the electrode is sacrificial and cannot berestored.

In some embodiments, the system comprises an electrode immersed inelectrolyte and fluidly and electronically coupled to an ion conductorin electrical contact with the nerve tissue.

In some embodiments, the ion conductor comprises a hydrogel material.

In some embodiments, the system comprises one or more current sourcesthat are connected via a lead to the one or more electrodes.

In some embodiments, the ion conductor includes a proximal layer, e.g.,screen or filter element to selectively sequester electrochemicalprocess byproducts to the electrolyte volume.

In some embodiments, the ion conductor includes a distal screen orfilter element to selectively sequester electrochemical processbyproducts from the nerve tissue.

In some embodiments, the ion conductor includes multiple screen orfilter elements to selectively sequester electrochemical processbyproducts from the nerve tissue.

In some embodiments, the system comprises materials which come incontact with tissue that are biocompatible.

In some embodiments, two or more systems to modulate the stimulustransmission along a nerve body include electron to ion currentconversion cells to change the electrical potential around the nerve andmodulate the nerve membrane potential.

In some embodiments, a method using two or more systems to maintain aconstant nerve block by delivering direct current in the form of ionsincludes operating one system in a blocking mode with current of onepolarity while the other system or systems are run in a mode withcurrent of the opposite polarity.

In some embodiments, a method of delivering a prolonged block to neuraltissue includes an initial delivery of current in the form of ionsproximal to the neural tissue to put the neural tissue into a suppressedstate where block continues after current ceases.

In some embodiments, a method of delivering a prolonged block to neuraltissue includes an initial delivery of current in the form of ionsproximal to the neural tissue to put the neural tissue into a suppressedstate where block continues after current ceases with subsequent currentdelivery to maintain the nerve in its suppressed state.

In some embodiments, a method of delivering a prolonged block to neuraltissue includes an initial delivery of current in the form of ionsproximal to the neural tissue to put the neural tissue into a suppressedstate where block continues after current ceases with subsequent currentdelivery to maintain the nerve in its suppressed state whereby currentof the opposite polarity between current delivery phases does not impactthe nerve suppression state.

In some embodiments, a system for accessing and modulating the nervesignal transmission properties of a DRG includes an introducer needlecomprising optionally radiopaque markers and a stylet and an electrodeconfigured to fit within the needle bore. The electrode comprisingstress-relief and securement features such as barbs and leads thatprovide electrical communication with a current source.

In some embodiments, a system for accessing and modulating the nervesignal transmission properties of the spinal cord includes an introducerneedle comprising optionally radiopaque markers and a stylet and anelectrode configured to fit within the needle bore. The electrodecomprising stress-relief and securement features such as barbs and leadsthat provide electrical communication with a current source.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of a DRG includes insertion of anintroducer needle into the body cavity to the nerve site, removing astylet, inserting an electrode, securing the electrode at the desiredtissue site, removing the needle, and connecting the EICCC electrodeleads to a current source and delivering a current to put the nerve in astate of suppression.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the spinal cord includes insertion ofan introducer needle into the body cavity to the nerve site, removing astylet, inserting an electrode, securing the electrode at the desiredtissue site, removing the needle, and connecting the EICCC electrodeleads to a current source and delivering a current to put the nerve in astate of suppression.

In some embodiments, the system includes an external current source.

In some embodiments, the system includes an implantable current source.

In some embodiments, the system includes a programmable current source.

In some embodiments, the system comprises a sensor proximal to the nervetissue to monitor the nerve tissue membrane potential and provide afeedback measurement for the current source.

In some embodiments, the system comprises a sensor that is an electrodethat serves as a reference electrode for the working electrode in theEICCC to monitor the electrode potential.

In some embodiments, a method for maintaining a nerve in a blocked stateis disclosed wherein the nerve membrane potential is monitored and usedas a signal to provide feedback to the current source and current sourcecontroller to enable modulation of the current source output to theelectrode.

In some embodiments, the system for delivery of ion current to neuraltissue comprises a current delivery source, a power supply, electricalconnection to an EICCC with a connector element to which an ionconducting electrode may be connected wherein the system is hermeticallysealed.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG is used to reduce pain due toneuralgias.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce paindue to angina.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce paindue to ischemic pain.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce paindue to complex regional pain syndrome (CPRS).

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce painin a specific region of the body.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce painin a specific limb of the body.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs is used to reduce painin a specific region of a limb of the body.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the DRG or DRGs can delivery differentcurrent signals to different DRGs for improved pain reduction coverage.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the spinal cord includes more than oneelectrode leads.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the spinal cord includes more than oneelectrode leads which include one or more regions that contact tissueand deliver current to the tissue.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the spinal cord includes more than oneelectrode leads at different levels along the spinal cord which includeone or more regions that contact tissue and deliver current to thetissue.

In some embodiments, the system for accessing and modulating the nervesignal transmission properties of the spinal cord includes more than oneelectrode leads which include one or more regions that contact tissueand deliver current to the tissue and can be individually adjusted todeliver the desired current and electric field to the tissue.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the spinal cord includes generatingpain relief as part of a peri-procedural pain block.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the spinal cord includes generatingpain relief as part of a peri-procedural pain block that is quicklyreversible.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of peripheral nerves to generate painrelief includes delivering direct current with an EICCC to peripheralnerve tissue to reduce focal pain.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of peripheral nerves to generate painrelief includes delivering direct current with an EICCC to peripheralnerve tissue to reduce phantom limb pain.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of peripheral nerves to generate painrelief includes delivering direct current with an EICCC to peripheralnerve tissue to reduce neuroma pain.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of peripheral nerves to generate painrelief includes delivering direct current with an EICCC to peripheralnerve tissue to reduce neuralgia pain.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of renal nerves includes reducingactivity of the sympathetic nervous system to reduce hypertension.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the sympathetic ganglia includesreducing activity of the sympathetic cervical ganglia to reduce heartfailure progression.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the sympathetic ganglia includesreducing activity of the sympathetic cervical ganglia to reduce orprevent tachycardia.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the vagus nerve includes reducingactivity of the vagus nerve to increase heart rate.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of the vagus nerves innervating thestomach includes reducing activity of the vagus nerve to increasesatiety and satiation.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of hepatic nerves includes reducingactivity of the sympathetic nervous system to increase insulinproduction.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of hepatic nerves includes reducingactivity of the sympathetic nervous system to reduce insulin resistance.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of brain tissue includes accessing thedesired region of the brain and reducing neural tissue activity to treatmovement disorders.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of brain tissue includes accessing thedesired region of the brain and reducing neural tissue activity to treatpsychiatric disorders.

In some embodiments, a method for accessing and modulating the nervesignal transmission properties of brain tissue includes accessing thedesired region of the brain and reducing neural tissue activity to treatchronic pain.

In some embodiments, disclosed herein is a system for nerve block of apatient utilizing a renewable electrode. The system can include a directcurrent generator, and/or at least one electrode comprising silverchloride. The system can also include a controller configured to signalthe direct current generator to deliver a first direct current with afirst polarity through the electrode sufficient to block conduction in anerve, and/or decrease an amount of the silver chloride in the electrodethereby forming solid silver and chloride ions. The controller can alsobe configured to signal the direct current generator to deliver a seconddirect current with a second polarity through the electrode sufficientto increase the amount of the silver chloride, thereby renewing theelectrode. The system can also include a nerve interface spaced apartfrom the electrode by a selective barrier. The selective barrier canalso be configured to allow chloride ions through the barrier toward thenerve interface to block the nerve. The system can also include a sensorconfigured to determine whether a reaction, such as a predominantlysilver/silver chloride reaction is occurring. The controller can befurther configured to receive data from the sensor and discontinue ormodulate at least one of the first direct current signal or the seconddirect current signal when water is being electrolyzed. The selectivebarrier can be further configured to prevent silver ions from passingthrough the barrier toward the nerve interface. The electrode can behoused in an insulated enclosure. The selective barrier can include anion exchange membrane, and/or a hydrogel. The system can be devoid ofany mechanically moving parts in some cases. The controller can beconfigured to deliver the first direct current such that the amount ofsilver chloride decreased is greater than a surface area of theelectrode prior to delivery of the first direct current. The controllercan also be configured to deliver the first direct current such that theamount of silver chloride decreased is greater than, such as about1.25×, 1.5×, 2×, 3×, 4×, 5×, 10×, 15×, 20×, 50×, 100×, 1,000×, or morean amount capable of evenly covering a surface area, such as the entirefunctional surface area of the electrode prior to delivery of the firstdirect current, or ranges including any two of the aforementionedvalues.

In some embodiments, also disclosed herein is a system for nerve blockof a patient utilizing a renewable electrode. The system can include oneor more of: a direct current generator; at least one electrodecomprising a solid component, an ionic component, and a nerve interfacedirectly adjacent the ionic component; a controller configured to signalthe direct current generator to: deliver a first direct current with afirst polarity through the electrode sufficient to block conduction in anerve and decrease an amount of the solid component; and/or deliver asecond direct current with a second polarity through the electrodesufficient to increase the amount of the solid component, therebyrenewing the electrode. The system can also include one or more sensorsconfigured to determine whether a predominantly solid component/ioniccomponent reaction is occurring. The controller can be furtherconfigured to receive data from the sensor and discontinue or modulateat least one of the first direct current signal or the second directcurrent signal when water is being electrolyzed. The electrode, or aplurality of electrodes, can be housed in an insulated enclosure, suchas the same or a different enclosure. The electrode can also include alayer, such as a selective barrier spaced between the ionic componentand the nerve. The layer can be configured to selectively allownegatively charged ions of the ionic component to pass through the layerand toward the nerve, and prevent positively charged ions of the ioniccomponent from passing through the layer toward the nerve. The systemcan be devoid of any mechanically moving parts. The nerve interface canbe spaced apart from the electrode by one or more of a gel, a hydrogel,and an ion conductive polymer. The electrode can be partially orcompletely surrounded by a solution, such as an electrolyte solution,e.g., isotonic saline. The solid component can include silver, and/orthe ionic component can include silver chloride. The controller can beconfigured to deliver the first direct current such that the amount ofsolid component decreased is greater than a surface area of the solidcomponent. The controller can also be configured to maintain the nervein a hypersuppressed state at least partially preventing conduction ofthe nerve for at least about 10 minutes or more after cessation ofdelivering of the first direct current.

In some embodiments, also disclosed herein is a method for nerve blockof a patient utilizing a renewable electrode. The method can include oneor more of delivering a first direct current of a first polarity throughan electrode comprising a first component proximate a nerve sufficientto block conduction in the nerve; and delivering a second direct currentof a second polarity opposite the first polarity through the electrode.The first direct current can decrease an amount of the first componentof the electrode thereby producing a second component different from thesecond component. The second direct current can increase the amount ofthe first component of the electrode and/or decreases the amount of thesecond component to renew the electrode. The method can also dynamicallysensing the amount of the first component or the second component in theelectrode while delivering the first direct current; and ceasingdelivery of the first direct current when the amount of the firstcomponent is sensed to reach a pre-determined threshold value, and/orwhen water is electrolyzed.

Also disclosed herein is a method for extended nerve block utilizing aplurality of renewable electrodes. The method can deliver a first directcurrent with a first polarity through a first electrode proximate anerve sufficient to block conduction in the nerve, the electrodecomprising a solid component and an ionic component; delivering a seconddirect current with a second polarity opposite the first polaritythrough a second electrode spaced axially apart from the first electrodeand proximate the nerve while the nerve is in the hypersuppressed state;and/or reversing the polarities of the first direct current and thesecond direct current, wherein reversing the polarities maintains thenerve in the hypersuppressed state.

In some embodiments, also disclosed herein is a method for extendednerve block utilizing at least one renewable electrode. The method caninclude delivering a first direct current with a first polarity to anelectrode proximate a nerve sufficient to block conduction in the nerve.Delivering the first direct current can place the nerve in ahypersuppressed state at least partially preventing conduction of thenerve after cessation of delivering of the first direct current. Themethod can also include delivering a second direct current with a secondpolarity opposite the first polarity through the electrode entirelywhile the nerve remains in the hypersuppressed state. The electrode canbe, for example, an electrochemical or capacitive electrode. Acapacitive electrode can include tantalum or titanium, for example. Theelectrode can include silver and/or silver chloride in some cases.Delivering the first direct current can change the electrode from afirst configuration to a second configuration, and delivering the seconddirect current transforms the electrode from the second configurationback to the first configuration, or at least closer to the firstconfiguration. The second configuration can include a lower amountand/or a lower charge than a material than the first configuration.

Also disclosed herein is a method for nervous tissue block utilizing atleast one renewable electrode. The method can include delivering a firstdirect current with a first polarity to an electrode proximate nervoustissue sufficient to block conduction in the nervous tissue. Deliveringthe first direct current can place the nervous tissue in ahypersuppressed state at least partially preventing conduction of thenervous tissue after cessation of delivering of the first directcurrent. The method can also include maintaining the nervous tissue inthe hypersuppressed state for at least about 1 minute, 10 minutes, 1hour, 24 hours, or more. The method can also include sensing theconduction ability of the nervous tissue, and/or maintaining the nervoustissue in a hypersuppressed state by delivering a third direct currentthrough the electrode to the nervous tissue after sensing the conductionability of the nervous tissue, wherein the third direct current has thesame polarity as the first direct current. Sensing the conductionability of the nervous tissue can include delivering a stimulus pulse tothe nervous tissue and measuring a compound action potential signal,and/or measuring potential differences via a reference electrode. Thenervous tissue could include one or more of a nerve, such as a spinal,cranial, or peripheral nerve, or brain tissue, dorsal root ganglia,tissue of the spinothalamic tract, autonomic nervous tissue, sympatheticnervous tissue, or parasympathetic nervous tissue. The direct currentcan be therapeutically effective to treat pain, such as acute or chronicpain and/or ischemic pain. The direct current can also betherapeutically effective to treat a psychiatric condition such asdepression, anxiety, obsessive-compulsive disorder, PTSD, mania, orschizophrenia; a movement disorder such as Tourette's syndrome,Parkinson's disease, spasticity, or essential tremor; and/or acardiopulmonary condition such as hypertension, congestive heartfailure, ischemic cardiomyopathy, angina, or an arrhythmia.

Also disclosed herein is a system for extended nerve block utilizing areversible electrode. The system can include one or more of a directcurrent generator; at least one electrode comprising a solid component,an ionic component, and a nerve interface adjacent the ionic component;a controller configured to signal the direct current generator to:deliver a first direct current with a first polarity through theelectrode sufficient to block conduction in a nerve; maintain the nervein a hypersuppressed state at least partially preventing conduction ofthe nerve after cessation of delivering of the first direct current;and/or deliver a second direct current with a second polarity throughthe electrode entirely while the nerve remains in the hypersuppressedstate.

Also disclosed herein is a method for providing extended nerve blockutilizing a renewable electrode. The method can include delivering afirst direct current of a first polarity through an electrode proximatea nerve sufficient to block conduction in the nerve, the electrodecomprising a first component and a second component; hypersuppressingthe nerve to at least partially prevent conduction of the nerve aftercessation of the first direct current; and/or delivering a second directcurrent of a second polarity opposite the first polarity through theelectrode while the nerve is in the hypersuppressed state. The firstdirect current can decrease an amount of the first component andincrease the amount of the second component. The second direct currentcan increase the amount of the first component and decreases the amountof the second component to renew the electrode. In some embodiments, themethod does not fully deplete the first component. The method can alsoinclude sensing the amount of at least one of the first component andthe second component; and ceasing delivering the first direct currentwhen the amount of the first component reaches a predetermined minimumthreshold value. A net charge delivered to the nerve after deliveringthe first direct current and the second direct current can be zero. Thefirst direct current can be an anodic or cathodic current and the seconddirect current can be a cathodic or an anodic current. The method canalso include sensing the conduction ability of the nerve, and/ormaintaining the nerve in a hypersuppressed state by delivering a thirddirect current through the electrode to the nerve after sensing theconduction ability of the nerve, wherein the third direct current hasthe same polarity as the first direct current. Sensing the conductionability of the nerve can include delivering a stimulus pulse to thenerve and measuring a compound action potential signal, and/or measuringpotential differences via reference electrode. In some embodiments,there can be a current-free gap in time in between delivering the firstdirect current of the first polarity and delivering the second directcurrent of the second polarity.

The method can also include delivering at least one, two, or moreadditional cycles of direct current. One cycle can include deliveringthe first direct current of the first polarity and delivering the seconddirect current of the second polarity opposite the first polaritythrough the electrode. The method can also include implanting theelectrode proximate the nerve, percutaneously positioning the electrodeproximate the nerve, and/or transcutaneously positioning the electrodeproximate the nerve. The nerve can be spaced apart from the electrode bya gel, a hydrogel, an ion conductive polymer, and/or a layer. Theelectrode can be partially or completely surrounded by an electrolytesolution, such as an isotonic saline solution.

In some embodiments a direct current delivery system could include anynumber of features or combination of features as disclosed herein.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A shows an embodiment of an EICCC electrode in which an electrodeis immersed in an electrolyte solution which is in contact with anion-conductive material-electrolyte solution interface with anion-conductive material that electrically contacts the nerve tissue N orarea proximal to the nerve tissue N.

FIG. 1B is a graph illustrating by pushing a constant current from thecurrent source, the mass of the AgCl electrode can decrease during acathodic current (reduction reaction) and then increase with an anodiccurrent during an oxidative reaction.

FIG. 1C shows how current being delivered to the electrode cell (EICCC)(top) can be associated with charge delivered to the electrodecell-nerve interface (middle) to provide nerve block (bottom) whileenabling zero net charge transfer with long charge phases, according tosome embodiments of the invention.

In FIG. 1D waveform patterns delivered to an electrode cell tofacilitate nerve block are shown in which current delivered to theelectrode cell is shown along with corresponding nerve block periodsincluding hypersuppression regions in which nerve block occursregardless of current being delivered to the nerve tissue, according tosome embodiments of the invention.

FIG. 1E shows an embodiment of an electron-ion current conversion cell(EICCC) which is connected via an electrically insulated lead to acurrent source.

FIG. 1F illustrates a configuration when the electron current is of onepolarity as designated by the positive axis, the nerve block is shown tobe active and when the polarity of the current is reversed as designatedby the negative axis, the nerve block is shown to be inactive.

FIG. 1G shows a similar configuration to FIG. 1E but with sequestrationscreens that respectively separate the traditional electrode from theion conductor and the ion conductor from the nerve itself.

FIG. 1H illustrates current vs. time and nerve block status vs. timecharts similar to FIG. 1F.

FIG. 1I shows a similar configuration to FIG. 1H but also includes afeedback sensor that monitors the state of the nerve tissue and/orregion proximal to the nerve N.

FIG. 1J illustrates current vs. time and nerve block status vs. timecharts similar to FIG. 1I.

FIG. 2A shows a dual electrode system in which two EICCCs interface witha nerve, according to some embodiments.

As shown in the graphs of FIG. 2B, two electrodes are driven withcurrents of opposite polarities as a function of time such that when oneis in an active blocking phase, the other is in an inactive non-blockingphase which resets the electrode for blocking once the current polarityis again reversed.

FIGS. 3A-B show an embodiment where dual traditional electrodesinterface with a nerve but are driven from a current source viaelectrically insulated leads with currents of opposite polarities suchthat when one is in a blocking phase, the other is in a non-blockingphase which resets the electrode for blocking once the current polarityis again reversed.

FIGS. 3C-D show an embodiment where dual EICCCs interface with a nerve Nbut are driven with currents of opposite polarities such that when oneis in a blocking phase, the other is in a non-blocking phase whichresets the electrode for blocking once the current polarity is againreversed.

FIG. 4A shows an embodiment of an EICCC electrode in which an electrodeis immersed in an electrolyte solution which fluidly in is contact withan ion-conductive material such as a hydrogel, gel or other polymer thatelectrically contacts the nerve tissue or area proximal to the nervetissue.

FIG. 4B shows a system similar to that shown in FIG. 4A with theaddition of a reference electrode in proximity to the electrode (workingelectrode) to monitor voltage drop across the working electrode forEICCC monitoring purposes.

FIG. 4C shows a system similar to that shown in FIG. 4A with theaddition of a reference electrode in proximity to the nerve tissueinterface to monitor voltage drop across the EICCC to the nerve tissuefor EICCC monitoring purposes.

FIGS. 4D-4F show an embodiment of an electrode lead configured to pluginto and extend from a current source (not shown, near end) that mighttake the form of conventional IPGs (implantable pulse generators).

FIG. 4G shows a schematic embodiment of an EICCC integrated within ahermitically sealed enclosure which contains the current source, batteryor power supply, and controller to drive the EICCC.

FIGS. 5A-B show an embodiment of an electrode configuration in which twoelectrode contacts are housed within the same electrically insulatedenclosure.

FIG. 6A illustrates a dorsal root, and/or dorsal root ganglion (DRG)through which pain signals pass.

FIG. 6B shows an embodiment of a blocking electrode positioned along aDRG to facilitate nerve block along with lead and current source.

FIG. 6C illustrates that a DRG can be accessed with a needle, and theneedle can be used to penetrate the dura mater as shown.

As shown in FIG. 6D and FIG. 6E, the electrode-nerve interface contactscan then be positioned in contact or proximal to the DRG and theintroducing needle can be retracted to leave the electrode lead andnerve tissue interface in the desired position.

FIG. 7 shows associated dorsal root ganglia from each vertebral levelcorrespond to specific dermatomes in the body, and blocking pain signalsat the DRG level can reduce pain sensation at the innervated dermatomefor that specific DRG.

FIG. 8A illustrates placement of stimulating electrodes in proximity tothe lateral spinothalamic tract (LT tract), which can leverage an EICCCto generate a nerve block at the desired level (and/or spinal levelsdistal (away from the head) to the EICCC since pain signals travel inthe superior direction) and provide selective pain block depending onunilateral (left or right) or bilateral placement of electrodes.

FIG. 8B illustrates a percutaneous placement procedure with or withoutfluoroscopic guidance such as by using a Tuohy or similar needle tointroduce the electrode lead into the epidural space.

The leads can be directed along the spinal column within the epiduralspace such that the lead is between spinal nerve exit regions and thetissue interface is in proximity to the lateral spinothalamic tract asillustrated in FIGS. 8C-8E.

FIG. 9A shows an electron-ion current conversion cell (EICCC) electrodeconfigured to interface with a deep brain block (DBB) target in thethalamus.

In FIG. 9B an embodiment of a blocking/suppressing electrode with anintegrated sensing electrode is shown.

An embodiment of an EICCC electrode is shown in FIGS. 10A-10C in whichmultiple tissue interfaces are present on the electrode and areindividually addressable.

FIG. 10B is a close-up view of 10B-10B of FIG. 10A.

FIG. 10C is a close-up view of 10C-10C of FIG. 10A.

As shown in FIG. 11, the blocking electrode leads contact the renalnerves to facilitate a block or suppression Also systematicallyillustrated is EICCC openly connected at to current source (not shown).

As shown in FIG. 12, the relevant sympathetic ganglia including thecervical and stellate (cervicothoracic) ganglia are shown along withtheir innervation targets in the heart.

FIG. 13 illustrates select sympathetic nervous system-related anatomy.

FIG. 14 illustrates an embodiment of an EICCC electrode placed around orin proximity to the right (and/or left) vagus nerve within the rightside of the neck and/or chest with an electrode lead running down towardan implantable current source shown in the right pectoral region.

FIGS. 15-16 illustrate an embodiment of a dual EICCC system in whicheach vagus nerve is wrapped in a cuff-format tissue interface at whichionic current is deposited at the tissue site from the EICCCs.

FIG. 17 schematically illustrates non-limiting anatomy where sympatheticnerve suppression or block can also be used to regulate hepatic functionand influence glucose and insulin production.

FIG. 18 illustrates an EICCC system in which the nerves around thehepatic artery and the artery are surrounded by a cuff-format tissueinterface, according to some embodiments of the invention.

DETAILED DESCRIPTION

This application describes, in some aspects, methods and systems formanagement of chronic and acute pain states via safe application ofdirect current (DC) to facilitate nerve block including nervehypersuppression, or nerve block without rapid reversibility or recoveryafter direct current application has been removed or stopped. Byinterfacing with the nerve via ionic conduction pathways instead ofconventional electrodes that that do not have an ionic conductioncomponent, an intermittent or continuous short term and long-term nerveblock can be generated while reducing risk of damage to the nerve cells.What is disclosed in some embodiments are systems and electrodes forsafely delivering blocking direct current (DC) to neural tissue bydelivering cycled cathodic and anodic current through a high-chargechemistry. Tissue safety can be maintained by separating the metalinterface from the nerve tissue with an ionically conductive element,and by operating the electrode below reaction potentials for undesiredreactions, such as electrolysis of water, or oxidation and reduction ofwater (H2O), which create harmful reactive species such as OH—, H+ oroxygen free radicals.

Chronic pain is a significant burden on individuals and society as awhole. Nearly 50 million adults are estimated to have significantchronic or severe pain in the US alone. (See Nahin, Estimates of PainPrevalence and Severity in Adults: United States, 2012, The Journal ofPain, 2015 Aug. 16(8): 769-780) Worldwide, chronic pain is estimated toaffect more than 1.5 billion people. (Borsook, A Future Without ChronicPain: Neuroscience and Clinical Research, Cerebrum, 2012 June) Whilesurgical techniques are sometimes applied to remove a specific source ofpain, typically due to impingement of a nerve, in many cases the precisecause of pain is not clear and cannot be reliably addressed via asurgical procedure. Pain management can alternatively be addressed byoverwhelming the central nervous system with stimulating signals thatprevent registration of pain inputs (gate control theory of pain).Typically, this stimulation in the case of spinal cord stimulation (SCS)is performed using metal electrodes and alternating current (AC)stimulation to produce these additional stimulating signals to preventpain sensation. However, one major drawback is the presence ofparesthesia, a sensation of tingling in the innervated region downstreamfrom the stimulated nerve. Methods to eliminate paresthesia whichpatients can find discomforting have led to different means ofstimulation from conventional tonic SCS (˜30-120 Hz) stimulationincluding high frequency stimulation (˜10 kHz) and burst stimulation(e.g., five pulses at 500 Hz delivered 40 times per second).(Tjepkema-Cloostermans et al, Effect of Burst Evaluated in PatientsFamiliar With Spinal Cord Stimulation, Neuromodulation, 2016 Jul.19(5):492-497).

An alternative means to manage pain signaling to the central nervoussystem is to prevent conduction of the pain signals from the peripheralsignal source by directly blocking the pain signals as compared tomasking the pain signals by generating alternative neural inputs tocrowd out and inhibit pain signal transmission as in traditional SCS andgate theory. One means to do this is by applying a direct current (DC)to a nerve to prevent action potential (AP) generation and transmission.Because this does not stimulate the nerve as in traditional stimulation,paresthesia can be avoided. The mechanism leading to AP block has beenattributed to a depolarization block that deactivates the sodiumchannels required for an action potential event under the electrodesite. (See Bhadra and Kilgore, Direct Current Electrical ConductionBlock of Peripheral Nerve, IEEE Transactions on Neural Systems andRehabilitation Engineering, 2004 Sep. 12(3): 313-324).

Bhadra et al. showed that upon application of DC to nerve tissue, actionpotential conduction can be blocked (See Bhadra and Kilgore, DirectCurrent Electrical Conduction Block of Peripheral Nerve, IEEETransactions on Neural Systems and Rehabilitation Engineering, 2004 Sep.12(3): 313-324). The authors showed that removal of DC delivery from thesame nerve tissue resulted in instantaneous restoration of nerveconduction. However, direct current has long been known to be dangerousto nerve tissue due to creation of toxic species at the electrode-nerveinterface (Merrill, Electrical Stimulation of Excitable Tissue: Designof Efficacious and Safe Protocols, Journal of Neuroscience Methods,2005, 141:171-198). Ackermann et al and Fridman et al have developedsystems and methods of safely delivering DC to nerve tissue byseparating the toxic species created at the electrode interface from thenerve tissue (U.S. Pat. Nos. 9,008,800 and 9,498,621; Ackermann et al,Separated Interface Nerve Electrode Prevents Direct Current InducedNerve Damage, J Neurosci Methods, 2011 September 201(1):173-176; Fridmanand Santina, Safe Direct Current Stimulation to Expand Capabilities ofNeural Prostheses, IEEE Transaction of Neural Systems and RehabilitationEngineering, 2013 Mar. 21(2):319-328; Fridman and Santina, Safe DirectCurrent Stimulator 2: Concept and Design, Conf Proc IEEE Eng Med BioSoc, 2013: 3126-3129), each of the foregoing of which are incorporatedby reference in their entireties. They also teach that rapidreversibility of nerve blockade is desirable and achievable throughhalting of DC delivery. Ackermann et al. teaches that an undesired, butreversible, suppression of nerve activity occurs with long term directcurrent delivery (where nerve tissue was shown to be non-conductive fora short period of time following cessation of DC delivery) (U.S. Pat.Nos. 9,008,800 and 9,498,621; Ackermann et al, Separated Interface NerveElectrode Prevents Direct Current Induced Nerve Damage, J NeurosciMethods, 2011 September 201(1):173-176), each of which are incorporatedby reference in their entireties. Those authors specifically teachmethods to reduce this suppression of nerve activity by limiting theduration of DC delivery to allow rapid nerve recovery upon cessation ofDC delivery (e.g., within seconds) (U.S. Pat. Nos. 9,008,800 and9,498,621; Ackermann et al, Separated Interface Nerve Electrode PreventsDirect Current Induced Nerve Damage, J Neurosci Methods, 2011 September201(1):173-176). What is invented and described herein in someembodiments are systems and methods for doing the opposite of that whichis taught by Ackermann et al: intentionally blocking nerve activity byusing periodic DC pulses to intentionally place neural tissue in a stateof hypersuppression without rapid reversibility upon cessation of DCdelivery (reversibility that occurs in many minutes to hours, as opposedto seconds or less than a minute). Furthermore, what is invented anddescribed herein in some embodiments are systems and methods of treatingpain by the aforementioned systems and methods, specifically throughselective blockade of antero-lateral column tissue in the spinal cord.Furthermore, what is invented and described herein are systems andmethods of treating pain by the aforementioned systems and methods,specifically through selective blockade of dorsal root tissue and/ordorsal root ganglia. Furthermore, what is invented and described hereinare systems and methods of treating pain by the aforementioned systemsand methods, specifically through blockade of one or more peripheralnerves.

With targeted nerve block, pain from specific dermatomes and pain inregional body sites can be managed. A number of localized targetsimplicated in moderating pain signal transduction can be addressed. Forexample, both more centrally located nerve tissues such as thespinothalamic tract and dorsal root ganglion can be targeted to managelower back pain, sciatica, and complex regional pain syndrome (CPRS)among other pain considerations.

Electrodes where current in the form of ions is generated proximal tothe at least one target nerve may comprise a ionically conductivematerial such as a liquid (e.g., saline or other electrolyte solution),gel, hydrogel, hydrocolloid, polymer, or film. In an alternativeembodiment, the ionically conductive materials may be separated by ascreen or other filter or membrane material from the nerve tissue. Thisseparating interface may be configured to selectively allow ions throughto the nerve to reduce nerve damage such as microporous screens,non-woven screens, ion-exchange membranes (IEM), supported liquidmembranes or ionogels, polymer electrolytes such as polyethylene oxide(PEO), polypropylene oxide (PPO), polyvinylidenefluoride-co-hexafluoropropylene copolymer (PVDF-HFP), solid ionconductors, and ion-selective films including cation exchange membranesand anion exchange membranes.

The nerve-interfacing element of the electrode may be further configuredto be exposed selectively along the electrode and may be otherwiseinsulated from the nerve by an ionically impermeable layer. Theimpermeable layer may also be configured to be electrically insulatingto current.

The ionically conducting material may also be separated into multipleregions which may contain different types of ionically conductingmaterial. The interfaces between the different regions may be delineatedby semi-permeable membranes or screens that allow for selective orgeneral ionic flow but limit the passage of damaging by products fromthe conversion of electron current to ionic current. This separatingelement may be configured to selectively allow ions through to the nerveto reduce nerve damage such as microporous screens, non-woven screens,ion-exchange membranes (IEM), supported liquid membranes or ionogels,polymer electrolytes such as polyethylene oxide (PEO), polypropyleneoxide (PPO), polyvinylidene fluoride-co-hexafluoropropylene copolymer(PVDF-HFP), solid ion conductors, and ion-selective films includingcation exchange membranes and anion exchange membranes. The differentionically conducting materials may also take different forms. As anexample, the nerve may be in contact with a hydrogel which is in contactwith a liquid such as an electrolyte solution which then is in contactwith a traditional electrical current electrode material.

In some embodiments the traditional electrode may be made from amaterial such as platinum, platinum-iridium, carbon, titanium nitride,copper, tantalum, silver, silver-chloride or other metals and materialsor combinations thereof. In some embodiments, the traditional electrodemay be made from carbon, graphite, glassy carbon, dendritic carbon, orother conductive materials. By using high-charge chemistry amplitude andduration of direct current (DC) block can be increased. Candidatechemistries include using a combination of Ag/AgCl electrode in anelectrolyte bath (or other suitable ionically conductive material) suchas saline that is in ionic contact with neural tissue of interest. Insome embodiments the electrode is reversible and can be restored to itsinitial state. In some embodiments the electrode is sacrificial and theelectrochemical reaction that occurs at the electrode cannot be reversedto restore the electrode to its initial state.

The combination of traditional electron-carrying electrode material andionic conducting material and the conversion mechanism can becollectively characterized as an electron-ion current conversion cell(EICCC). One such example might be a silver/silver chloride (Ag/AgCl)electrode immersed in a saline, e.g., isotonic 0.9% NaCl saline solutionfluidly in contact with a saline-containing hydrogel. Upon driving of anelectric current through the conventional electrode, reduction of thesolid AgCl will drive conversion to solid Ag and Cl-ion formationgenerating a flow of ions or an ion current. This ionic current flow canbe used to modulate the nerve membrane potential and, for example,create a blockade of nerve conduction. The membrane potential may bemodulated in such a manner that the potential is ramped up slowly enoughto avoid action potential generation as the nerve tissue is depolarized.Upon reversal of the electric current, oxidation of the previouslyformed Ag or other Ag in the Ag/AgCl electrode will be oxidized togenerate AgCl deposits on the electrode, driving the ion current in theopposite direction. Due to the extremely low solubility of Ag and AgClin saline, the electrode remains mechanically intact during forward andreverse current delivery. In combination, the reduction-oxidationreactions create a fully reversible EICCC. To maintain the preferredreduction-oxidation reaction between Ag and AgCl (or other electrodematerials), the amount, e.g., mass, volume, density, or anotherparameter of the AgCl on the electrode may be maintained within 5%-95%,10%-90%, 20%-80%, 25%-75%, 30%-70% of its original starting mass on theelectrode to ensure that the AgCl is never depleted or saturated,enabling other deleterious reactions from happening at the electrode. Insome embodiments, the amount of the electrode can be maintained at leastabout, or no more than about 5%, 10%, 15%, 20%, 25%, 30%, 35%, 40%, 45%,50%, 55%, 60%, 65%, 70%, 75%, 80%, 85%, 90%, 95%, 100%, or ranges ofbetween about any two of the foregoing values. In other words, theelectrode is reversible and can be restored to its original orsubstantially to its near-original state. To generate more surface areafor the electrochemical reactions to occur, the traditional electrodesmay be made from high surface area to volume structures such asroughened surfaces, woven surfaces, patterned surfaces, reticulated foamstructures, porous sintered bead structures, nano- or micro-patternedstructures to expose additional material surface area. High-chargechemistry electrodes can be biocompatible, or suitably sequestered frombody if not. A high surface area electrode material (e.g. Ag/AgCl) inthe EICCC may be utilized specifically to decrease the electrodepotential drop or to reduce the increase in electrode potential dropwhich may occur with prolonged current delivery. In some embodiments theEICCC driving current may be between about 0 mA and about 1 mA, betweenabout 1 mA and about 2 mA, between about 2 mA and about 4 mA, betweenabout 4 mA and about 8 mA, higher than about 8 mA, about 0.5 mA, 1 mA, 2mA, 3 mA, 4 mA, 5 mA, 6 mA, 7 mA, 8 mA, 9 mA, 10 mA, or rangesincorporating any two of the foregoing values. In some embodiments thisdriving current is then used to generate a corresponding ionic currentof similar magnitude, depending on the specific electrochemicalreactions.

Another embodiment of the EICCC may comprise a material such as tantalumor titanium nitride to generate a capacitive traditional electrodeinterface instead of an interface at which an electrochemical reactionoccurs. Transparent conducting oxides (TCOs) such as fluorine-doped tinoxide (FTO), nickel titanium dioxide (Ni/TiO2), and other titaniumdioxide (TiO2) constructs are also candidate materials that have highcharge carrying capacities. In this configuration, charge generation atthe traditional electrode surface would attract ionic species from theionically conductive material until the charge at the traditionalelectrode interface is passivated. Charging of the capacitive materialwith an electric current of one polarity can generate current flow inthe form of ions. Reversing the polarity of the current flow to thecapacitive material can effectively reset the system for a subsequentcharging to generate further ionic current flow. To generate moresurface area for increased ion current flow capacity to occur, thetraditional electrodes may be made from high surface area to volumestructures such as roughened surfaces, reticulated foam structures,porous sintered bead structures, nano- or micro-patterned structures toexpose additional material surface area. In one embodiment, thiscapacitive structure is in fluid contact with an electrolyte solutionthat contacts an electrolyte-saturated hydrogel in contact with targetnerve tissue to enable ion current flow to the tissue.

In a further embodiment of the EICCC, a combination of bothelectrochemical and capacitive mechanisms may be used to convert currentin the form of electrons to current in the form of ions.

To deliver ionic current to the nerve to facilitate a block, thetraditional electrode may be connected via a conductive lead to one ormore current sources. A single nerve-electrode interface can providenerve block when current is applied in one polarity to the EICCC(blocking phase). When the current polarity is reversed to return theelectrode to its original state (which may be a non-blocking phase oralso a blocking phase), the nerve may or may not continue to block painstimulus from passing along the nerve. If the nerve has been placed intoa state of hypersuppression, the nerve will continue to prevent APpropagation and block pain regardless of the phase state of theelectrode. Fridman and Santina have described a means to enablecontinuous block when current polarity is reversed as driven by analternating current (AC) using a series of valves to direct current flowdirection (Fridman and Santina, Safe Direct Current Stimulation toExpand Capabilities of Neural Prostheses, IEEE Transaction of NeuralSystems and Rehabilitation Engineering, 2013 Mar. 21(2):319-328; Fridmanand Santina, Safe Direct Current Stimulator 2: Concept and Design, ConfProc IEEE Eng Med Bio Soc, 2013: 3126-3129). However, in some cases itis desirable to have a more simple system which does not require the useof valves which present additional failure points and add bulk to animplantable system. A simpler, more robust system may be configuredwithout valves and such moving parts by using multiple EICCCs to provideconstant stimulation of the nerve tissue itself. In one embodiment toprovide continuous block, two nerve-electrode interfaces are present andconnected to one or more current sources. The first nerve-electrodeinterface EICCC is run with the current in one polarity to drive a blockwhile the second nerve-electrode interface EICCC is run with theopposite polarity. After a period of time, the current polarities of thefirst and second EICCCs are reversed and the second nerve-electrodeinterface provides a block while the first nerve-electrode interfaceEICCC state is reversed to its prior state. By cycling the dual-EICCCelectrode currents, a continuous block can be maintained at the targetnerve. As can be appreciated, more than two, such as 3, 4, 5, 6, 7, 8,9, 10, or more EICCCs may also be used to facilitate the same continuousblock. Electrodes may also be run in either monopolar or bipolarconfigurations. In some embodiments the EICCC system is configured tonot have any mechanically moving parts such as valves or hinges.

Alternatively, nerve activity may be suppressed which means that nerveactivity remains blocked even after removal or discontinuation of theblocking current. The nerve may be further put into a state ofhypersuppression in which the nerve remains blocked without rapidreversibility after cessation of DC delivery. Modulation of the initialcurrent delivered to the nerve tissue including ramp rate, currentamplitude, total charge delivery, and waveform shape can be used toplace the nerve in a state of suppression. During the state ofsuppression, the EICCC may be returned to its initial state by reversingthe current polarity used to generate the initial block and suppressionstate. During the period of reverse current flow, the nerve may remainin a state of hypersuppression. In another configuration the EICCC maydeliver subsequent blocking current inputs that extend the suppressionduration, with periods of no current delivery, or of reversal current inbetween blocking current doses. The nerve tissue may remain in a stateof hypersuppression during the periods of non-blocking current input. Inanother configuration, the EICCC may be configured to deliver subsequentcurrent inputs on a schedule. In some embodiments, the DC block waveformmay have an amplitude of between 0-250 microamps, 250-500 microamps,500-1000 microamps, 1000-1500 microamps, or 2000 microamps, or higher,or about, at least about, or no more than about 50, 100, 150, 200, 300,400, 500, 600, 700, 800, 900, 1,000, 1,100, 1,200, 1,300, 1,400, 1,500,1,600, 1,700, 1800, 1,900, 2000 microamps or more, or other rangesincorporating any two of the aforementioned values. Placing a nerve intoa state of hypersuppression may be facilitated in some embodiments bydelivering a charge of 10-50 millicoulombs, 50-100 millicoulombs,100-500 millicoulombs, 500-1000 millicoulombs, or 1000 millicoulombs orgreater, or about, at least about, or no more than about 10, 25, 50,100, 200, 300, 400, 500, 600, 700, 800, 900, 1,000, or moremillicoulombs, or other ranges incorporating any two of theaforementioned values, and depending on nerve size and desiredhypersuppression duration. DC block amplitude and current duration maybe tuned to enable hypersuppression in the range of, for example, 0-0.5times the duration of initial DC block, 0.5-1 times the duration ofinitial DC block, 1-1.5 times the duration of initial DC block, 1.5-2times the duration of initial DC block, and greater than 2 times theduration of initial DC block, or about, at least about, or no more thanabout 0.1×, 0.2×, 0.3×, 0.4×, 0.5×, 0.6×, 0.7×, 0.8×, 0.9×, 1×, 1.1×,1.2×, 1.3×, 1.4×, 1.5×, 1.6×, 1.7×, 1.8×, 1.9×, 2×, 2.5×, 3×, 4×, 5×, ormore relative to the duration of initial DC block, or ranges includingany two of the aforementioned values.

Sensing the local state of and proximal to the nerve tissue can alsoprovide a useful measure for determining when to provide current inputsto extend nerve suppression as well as to provide a feedback loop forinitial current delivery to generate the initial nerve block bymodulating the nerve potential such that it cannot transmit actionpotentials. In one embodiment the nerve's ability to conduct actionpotentials is monitored such that as direct current is delivered to thenerve tissue, the direct current delivery can be maintained to ensurethat the nerve block is maintained, for example. Nerve conductionability may be monitored by any suitable measure such as delivering astimulus pulse and measuring compound action potential signal.

In some embodiments sensing is in the form of a reference electrode tomeasure potential differences relative to the two electrodes which arepassing the active current. In some embodiments the active current ismodulated in response to one or more measured electrode potentialsrelative to the reference electrode. In some embodiments the activecurrent is modulated when measured electrode potential indicates thatundesired electrochemical reactions may occur at one or more activeelectrodes. For example, active current may be reduced or ceased uponmeasurement of an active electrode potential that indicates waterelectrolysis is occurring or possible. The EICCC may be operated with adirect current input or by applying a potential difference between theworking electrode and an auxiliary or counter electrode. In someembodiments, a reference electrode may be located within the EICCC or atthe distal end of the EICCC proximal to the nerve tissue.

FIG. 1A shows an embodiment of an EICCC electrode 100 in which anelectrode 104 is immersed in an electrolyte solution 102 which in iscontact with an ion-conductive material—electrolyte solution interface107 with an ion-conductive material 106 such as a fluid, hydrogel, gelor other polymer that electrically contacts the nerve tissue N or areaproximal to the nerve tissue N. The EICCC electrode 100 also comprisesan electrically insulated, biocompatible enclosure 108 housing thetraditional electrode 104, electrolyte 102, and biocompatible ionconducting material 106 with an aperture (near 110) to enable electricalcontact with the nerve N or area proximal to the nerve tissue N. Thesystem further comprises a current delivery lead 112 between the currentsource 114 and the electrode 104. The current source 114 may be locatedexternal or internal to the body depending on the application need. Anexemplary non-limiting embodiment of the EICCC 100 comprises a silver,silver-chloride (Ag/AgCl) electrode in a 0.9% saline solution in fluidcontact with an electrolyte saturated hydrogel (agar preparation with0.9% saline).

With an Ag/AgCl electrode used to generate current via reduction of theAgCl on the electrode in a saline solution (NaCl), a sustainable andreversible electrochemical reaction can be achieved to convert currentin the form of electrons into current in the form of ions. As seen inRegion 1 of FIG. 1B, by pushing a constant current from the currentsource, the mass of the AgCl electrode will decrease from mass m2 tomass m1 during a cathodic current (reduction reaction) and then increaseas seen in Region 2 from mass m1 back to mass m2 with an anodic currentduring an oxidative reaction. Furthermore, it can be appreciated that bylimiting the maximum mass of the AgCl to m2 such that the mass ofunreacted Ag is greater than zero helps prevent the Ag/AgCl reactionfrom depleting available Ag for the electrochemical reaction andprovides a reserve safety factor in the event of excess current deliverysimilar to maintaining m1 above zero. In Region 3, the current polarityis again reversed to match that of Region 1. By not depleting the AgClmass to zero, the preferred reaction between conversion of solid AgCl tosolid Ag with generation of chlorine ions and vice-versa:AgCl(s)+e ⁻⇔Ag(s)+Cl⁻Because water electrolysis or hydrolysis happens at higher reductionpotential than AgCl, AgCl dissolution will be preferred preventingundesired reactions and generation of OH—, H+ or oxygen free radicals inthe EICCC. Further notable is that the absolute value of the areabetween the current amplitude and the x-axis (time) can be used todefine the total charge delivered (or removed) from the electrode toallow for determination or prediction and/or control of the electrodeAgCl mass. It will be appreciated that the current waveform shapes inthe different regions need not be perfect square waves but may includefinite slopes that ramp from zero amplitude to their final maximumamplitude as well as from their maximum waveform amplitude back to zerocurrent. Waveforms may also be non-linear in pattern and may varybetween regions. In a preferred embodiment, the total charge deliveredin Region 1 is equivalent to the total charge removed in Region 2. Inother words, the magnitude of the area below the current waveform inRegion 1 is the same as that of Region 2. Different regions may also bespaced apart in time by a period of zero current (not shown) in whichthe AgCl electrode mass is conserved while no current is beingdelivered. Not to be limited by theory, the silver-silver chloridesystem offers several potential benefits over other electrochemicalreactions. For example, the standard potential of the silver-silverchloride reaction is about 0.22 V, which is advantageously well belowthe voltage at which electrolysis occurs. Electrolysis can occur whenthe magnitude of potential or voltage used to drive a reaction exceedsabout 1.23 volts referenced against the standard hydrogen electrode.Electrolysis of water can be detected via one or more sensors, and ceaseor modulate (increase or decrease) current delivery and/or drivingvoltage if electrolysis is detected in some cases. The sensors can alsodetect in some cases whether the silver-silver chloride reaction isexclusively, substantially exclusively, or predominantly occurringrather than electrolysis, hydrolysis, or a redox water reaction, forexample. Furthermore, the amount of charge that can be delivered by sucha system is not limited by surface area reactions such as in the case ofplatinum electrodes which form a monolayer of platinum-hydride on theelectrode surface before the available platinum for reaction isexhausted leading to other potentially harmful products forming if thereaction is continued to be driven. In contrast, in an aqueousenvironment when silver-chloride is reduced it forms solid silver andreleases a chloride ion into solution and vice-versa. The reaction ineach direction is only limited by the quantity of reactant available sothe reaction is in effect limited by the total volume of reactantavailable compared to being limited to surface area. As such, thereaction can utilize an amount of reactant greater than that of theinitial, unreacted surface area of the electrode, such as about or atleast about 110%, 120%, 130%, 140%, 150%, 160%, 170%, 180%, 190%, 200%,250%, 300%, 500%, 1,000%, 5,000%, 10,000%, 25,000%, 50,000%, 100,000%,500,000%, 1,000,000%, 2,500,000%, 5,000,000%, 10,000,000%, 25,000,000%,50,000,000%, 100,000,000%, 250,000,000%, 500,000,000%, 1,000,000,000%,or more of the initial total, unreacted surface area of the electrode,or ranges including any two of the aforementioned values and dependingon the volume of silver utilized. Therefore, substantially more, and insome cases orders of magnitude more charge can be advantageouslydelivered to body tissue while remaining below the electrolysisthreshold. For example, a platinum or platinum-iridium electrode mightdeliver 5 microcoulombs per pulse in a 5 mA pulse for 1 millisecond.With embodiment as disclosed herein, it can be possible to achieve aboutor at least about 1,000×, 5,000×, 10,000×, 50,000×, 100,000×, or moretimes this charge using DC delivery in the form of a 5 mA pulse with 10second duration. This may be achieved, for example, by creating a 1micron coating of AgCl on an electrode of nominal geometry of 3.5 mmlength (or between about 1 mm and about 10 mm in length, between about 1mm and about 5 mm in length, or between about 3 mm and about 4 mm inlength) and 1.4 mm diameter (or between about 0.5 mm and about 5 mm indiameter, between about 0.5 mm and about 3 mm in diameter, or betweenabout 1 mm and about 2 mm in diameter) comparable to existing platinumelectrodes. One skilled in the art will appreciate that depending onconfiguration and reservoir of silver-chloride available, the amount ofcharge delivered can increase to 10,000×, 100,000×, 1,000,000×,10,000,000×, 100,000,000× or more, or ranges incorporating any two ofthe aforementioned values, compared to that achievable using aconventional platinum electrode. The silver-silver chloride complex canthus be uniquely situated for use in body environments because thereaction chemistry involves chloride ions which are one of the mostreadily available ions in and around body tissue.

FIG. 1C shows how current being delivered to the electrode cell (EICCC)(top) can be associated with charge delivered to the electrodecell-nerve interface (middle) to provide nerve block (bottom) whileenabling zero net charge transfer with long charge phases. In Phase 1,charge can be delivered to the electrode cell with a given polarity andconstant or variable ramp rate (R1) to then provide a constant orvariable current (C1) with subsequent constant or variable ramp (R2)back to zero current. Phase 1 may be, for example, of duration up to 1second, 1 minute, 1 hour, 1 day, 1 month, or 1 year, or longer. In someembodiments, Phase 1 average current is non-zero, but instantaneouscurrent may at times be zero. In some embodiments, Phase 1 is eithercathodic or anodic but not both. The initial phase, Phase 1, may befollowed by an interphase interval (Interval 1) between cathodic andanodic phases that is greater than or equal to zero seconds. Subsequentto this interval, a second current delivery phase (Phase 2) which may beof duration up to 1 second, 1 minute, 1 hour, 1 day, 1 month, or 1 year,or longer can be applied. This second phase is of opposite polarity toPhase 1 where average current is non-zero, but instantaneous current mayat times be zero. In Phase 2, charge can be delivered to the electrodecell with a given polarity and constant or variable ramp rate (R3) tothen provide a constant or variable current (C2) with subsequentconstant or variable ramp (R4) back to zero current. This Phase 2 maythen be followed by another interphase interval (Interval 2) that isgreater than or equal to zero seconds. The waveform in FIG. 1C may berepeated with identical or differing amplitude and duration parametersas a previous waveform whereby the waveform may be programmed oradjusted by a clinician and/or patient and/or caregiver and/or controlsystem. Adjustments may include adjusting the currents in Phase 1 andPhase 2 such that currents are ramped up and/or down as well asadjusting the durations of the phases t1-t0 and t3-t2, respectively.Interphase intervals can also be adjusted such that their durationst2-t1 and t4-t3 are lengthened or shortened. Any delivery or interphaseperiod could be, for example, at least about, about, or no more thanabout 1, 5, 10, 15, 20, 25, 30, 35, 40, 45, 50, or 55 seconds; 1, 2, 3,4, 5, 6, 7, 8, 9, 10, 15, 30, 60, 120 minutes; 3, 4, 5, 6, 7, 8, 9, 10,12, 16, 18, or 24 hours; 2, 3, 4, 5, 6, 7, 14, 21, 28, 30, 45, 60, 75,90, or more days; 4, 5, 6, 7, 8, 9, 10, 11, 12, 18, 24 or more months;or ranges including any two of the aforementioned values.

At the nerve interface the current delivered to the electrode cell cangenerate an increase in charge (positive or negative) delivered to thenerve interface as shown and may be linear as shown or generallyincreasing in a linear or non-linear fashion in Phase 1. The net chargedelivered remains roughly constant during the gap phase or Interval 1then returns to zero during Phase 2. Initially, the period of nerveblock (FIG. 1C bottom) is initiated somewhere during the beginning ofPhase 1 and nerve block will remain active (solid line) while charge isbeing delivered to the nerve interface. However, nerve suppression asdefined by continued nerve block after removal of current delivery tothe electrode cell may continue after current delivery to the nerve isstopped and may persist into the Interval 1 period (ii), extend intoPhase 2 (iii) independent of the opposite polarity current beingdelivered, or into Interval 2 (iv), or beyond (not pictured). Tuning ofthese parameters can lead to the placement of the nerve into a state ofhypersuppression as seen in FIG. 1C (ii), (iii), (iv) in which nervesuppression may occur for durations greater than one minute afterremoval of DC delivery.

In FIG. 1D waveform patterns delivered to an electrode cell tofacilitate nerve block are shown in which current delivered to theelectrode cell is shown along with corresponding nerve block periodsincluding hypersuppression regions in which nerve block occursregardless of current being delivered to the nerve tissue. The electrodecell system is designed such that the cathode and/or anode phase isdesigned to place the neural tissue in a state of not being conductive(or partially conductive) after the cessation of the current for periodslonger than one minute (hypersuppression) after current delivery. InFIG. 1D(i) an electron current has been delivered to the electrode cellto generate an ion current at the neural tissue facilitating a nerveblock. After this initial current delivery, the neural tissue thenenters a state of hypersuppression whereby in the absence of additionalcurrent delivery to the neural tissue, the nerve cannot conduct signalsor is not fully conductive. The neural tissue suppressed state may alsobe extended as shown in FIG. 1D(ii) in which a secondary current isdelivered to the neural tissue a period of time after the initialcurrent has been delivered where the delivery of the extension currentmay occur up to one minute after the initial current is delivered orafter periods of longer than one minute (hypersuppression). This patternof suppression extension may be repeated for a defined period of time orindefinitely with constant or variable length intervals between currentdelivery phases. To maintain the electrode cell in a charge neutralstate over repeated uses, current with opposite polarity may be appliedafter the initial nerve block current is applied and has placed thenerve into a state of hypersuppression (FIG. 1D(iii)). Subsequently,current of the original polarity can be applied to induce additionalhypersuppression extension as shown. In this manner the nerve tissue canbe repeatedly “dosed” with anodic and/or cathodic safe DC current tomaintain the neural tissue in a state of hypersuppression. Thehypersuppression duration is longer in duration than a cathodic and/oranodic delivery phase, allowing for complete net charge reversal duringhypersuppression. In these examples, the duration and/or amplitude ofthe cathode and/or anode phase(s) can be programmed to influence theduration and completeness of the nerve block after current delivery hasstopped.

FIG. 1E shows an embodiment of an electron-ion current conversion cell(EICCC) 100 which is connected via an electrically insulated lead 112 toa current source 114. The EICCC 100 comprises a traditional electrode(electrode) 104 material (e.g., metal, carbon, etc.) connected to anionically conductive material (ion conductor 106) which then interfaceswith the nerve tissue N, or tissue in proximity to nerve tissue. In someembodiments, the interface can be within about 3 cm, 2.5 cm, 2 cm, 1.5cm, 1 cm, 5 mm, 2 mm, 1 mm, 0.5 mm, 0.1 mm, or less in proximity tonerve tissue. One skilled in the art will appreciate that theconventional electrode 104 and ionically conductive material 106 may beattached in a multitude of ways such as shown abutting or in aninterlocking fashion and the like. The electrode 104 may be insertedwithin the ion conductor 106 or vice-versa. As shown in FIG. 1F, in oneconfiguration when the electron current is of one polarity as designatedby the positive axis, the nerve block is shown to be active and when thepolarity of the current is reversed as designated by the negative axis,the nerve block is shown to be inactive. It should be appreciated thatin the case in which the initial blocking current is applied to thenerve N in such a manner to induce a state of hypersuppression, thenerve may remain N blocked during the current reversal period. Duringthe current reversal period, the EICCC 100 is in a resetting phase inwhich the reaction used to generate the ion current is reversed to bringthe EICCC 100 components back towards their original state forsubsequent blocking current generation.

FIG. 1G shows a similar configuration to FIG. 1E but with sequestrationscreens 118, 120 that respectively separate the traditional electrode104 from the ion conductor 106 and the ion conductor 106 from the nerveN itself, or nerve adjacent tissue. One of ordinary skill in the artwill appreciate that one, two, or more or no screens may be used, or anycombination thereof. The screens 118, 120 are configured to selectivelyallow certain ions to transfer between the respective materials whilerestricting the movement of other ions whose movement is not desired,for example to maintain reaction species such as Cl— near the electrode.The screens 118, 120 may be comprised of an ionically selective membranesuch as an anion exchange membrane that only allows anions to passthrough it. FIG. 1H illustrates current vs. time and nerve block statusvs. time charts similar to FIG. 1F.

FIG. 1I shows a similar configuration to FIG. 1G but also includes afeedback sensor 122 that monitors the state of the nerve tissue N and/orregion proximal to the nerve N. In some embodiments a sensor 122 may belocated proximal or distal to the electrode-nerve interface in order toenable measurement of local compound action potential to providefeedback to the current source 114 and EICCC 210 to enable it tomodulate electrode current and nerve interface electrode potential tomaintain hypersuppression. In some embodiments the sensor 122 maymeasure nerve tissue voltage signals and use that information asfeedback to modulate the current and electric potential generated at thenerve interface. In some embodiments the electric potential is modulatedsuch that the nerve cells are maintained in a depolarization state inwhich action potentials cannot propagate along the nerve cells. In someembodiments the sensor 122 comprises a reference electrode whereby thepotential difference between one or more working electrodes 104 and thereference electrode can be monitored and used as feedback to the currentsource 114 to ensure proper operating range of the EICCC 210. Theimplantable packaging may contain an integrated reference or counterelectrode. FIG. 1J illustrates current vs. time and nerve block statusvs. time charts similar to FIG. 1H.

FIG. 2A shows a dual electrode system in which two EICCCs 220A, 220Binterface with a nerve N or nerve adjacent tissue. The two electrodes220A, 220B are driven with currents of opposite polarities as a functionof time such that when one is in an active blocking phase, the other isin an inactive non-blocking phase which resets the electrode forblocking once the current polarity is again reversed as shown in FIG.2B. With this configuration a constant block can be maintained along thenerve N. It should be appreciated that in the case in which a blockingcurrent is applied to the nerve N in such a manner to induce a state ofhypersuppression, the nerve block may remain active during the currentreversal period of the electrodes 220A, 220B. One skilled in the artwill appreciate that the driving currents for the two electrodes 220A,220B may be spaced apart in time during which no current is driving oneor both electrodes 220A, 220B and that during this period block may bemaintained if the nerve N is in a state of suppression. Similarly, thedriving currents may be of different durations dependent on theelectrodes 220A, 220B themselves and any recovery time of the nerve Nduring which signal remains blocked while no blocking current is beingapplied. The electrodes 220A, 220B may be oriented as shown in seriesaxially along a nerve N or oriented on opposite sides to the nervetissue itself.

FIGS. 3A-B show an embodiment where dual traditional electrodes 104A,104B interface with a nerve N but are driven from a current source viaelectrically insulated leads 112 with currents of opposite polaritiessuch that when one is in a blocking phase, the other is in anon-blocking phase which resets the electrode for blocking once thecurrent polarity is again reversed. With this configuration a constantblock can be maintained along the nerve. The electrodes 104A, 104B maybe oriented as shown in series along a nerve N or oriented on oppositesides to the nerve tissue itself.

FIGS. 3C-D show an embodiment where dual EICCCs 230A, 230B interfacewith a nerve N but are driven with currents of opposite polarities suchthat when one is in a blocking phase, the other is in a non-blockingphase which resets the electrode for blocking once the current polarityis again reversed. With this configuration a constant block can bemaintained along the nerve N as illustrated in FIG. 3D. The electrodes230A, 230B interface with the nerve N via screens that sequesterdeleterious byproducts from dangerous electrochemical reactions toprotect the nerve N. The screens may include an ionically selectivemembrane such as an anion exchange membrane that only allows, forexample, anions to pass through it (but not cations).

FIG. 4A shows an embodiment of an EICCC electrode 240 in which anelectrode 104 is immersed in an electrolyte solution 102 which fluidlyin is contact with an ion-conductive material 106 such as a hydrogel,gel or other polymer that electrically contacts the nerve tissue N orarea proximal to the nerve tissue. The EICCC 240 electrode alsocomprises an electrically insulated enclosure 108 housing thetraditional electrode 104, electrolyte 102, ion conducting material 106with an aperture (near 110) to enable electrical contact with the nerveor area proximal to the nerve tissue. The electrolyte-hydrogel 107interface can alternatively be mediated by an ion selective screen or anion conductive polymer to sequester by products of any electrochemicalreactions to the aqueous region of the cell. The system furtheroptionally comprises a current delivery lead 112 between the currentsource 114 and the electrode 104. The current source 114 may be locatedexternal or internal to the body depending on the application need. Anexemplary embodiment of the EICCC 240 comprises a silver,silver-chloride (Ag/AgCl) electrode in a 0.9% saline solution in fluidcontact with an electrolyte saturated hydrogel (agar preparation with0.9% saline). In other examples, the electrode material may comprisemetal, carbon, conductive polymers materials and may be configured in ahigh surface area to volume configuration that may includeconfigurations such as open-celled foam configurations, sinteredparticle configurations, dendritic configurations or the like.

FIG. 4B shows a system 250 similar to that shown in FIG. 4A with theaddition of a reference electrode 111 in proximity to the electrode(working electrode) 104 to monitor voltage drop across the workingelectrode 104 for EICCC monitoring purposes. For example, to ensure thatthe electrode 104 is being driven under the desired conditions to ensurethat the proper electrochemical reactions are occurring.

FIG. 4C shows a system 260 similar to that shown in FIG. 4A with theaddition of a reference electrode 111 in proximity to the nerve tissueinterface to monitor voltage drop across the EICCC 260 to the nervetissue for EICCC monitoring purposes. For example, to ensure that theelectrode 104 is being driven under the desired conditions to ensurethat the proper electrochemical reactions are occurring.

FIGS. 4D-F show an embodiment of an electrode lead 212 configured toplug into and extend from a current source (not shown, near end 213)that might take the form of conventional IPGs (implantable pulsegenerators). FIG. 4F is a close-up view of 4E-4E of FIG. 4D. FIG. 4F isa close-up view of 4F-4F in FIG. 4D. This configuration could be similarto as that shown in FIG. 4A except that the nerve interface hydrogelshown in FIG. 4A is removed and the nerve tissue interface comprises ascreen or porous frit 404 which contains the electrolyte solution butallows ions to pass to the nerve tissue environment. A connector 213 tothe current source is shown with an electrically conductive portion ofthe electrode lead 213 that extends distal from the connector 213 to theEICCC 400 which couples the electron current to an ionic current viaelectrochemical reactions. The coiled electrode 402 converts electricalcurrent to ionic current in the EICCC 400 which is then transmittedtoward the distal portion of the lead which can be positioned inproximity to the target nerve tissue. Contact with the nerve tissueenvironment occurs via the ionic current which exits the screen/porousfrit 404 that can manipulate the nerve environment.

FIG. 4G shows a schematic embodiment of an EICCC integrated within ahermitically sealed enclosure 410 which contains the current source 412,battery 414 or power supply, and controller 416 to drive the EICCC 280.The EICCC 280 is directly connected to the current source 412 asillustrated and comprises a lead 418 from the current source 412 and anelectrode 420 immersed in an electrolyte solution 429 which fluidly isin contact with an ion conductive material 422 such as a hydrogel whichin turn contacts the nerve tissue N to be blocked. In this embodimentthe electrode element 420 of the EICCC 280 is located relativelyproximal to the current source 412 while the nerve contacting lead islocated relatively more distally from the current source 412 and extendsto the nerve location N. Also illustrated is the ion conductive conduit(e.g. hydrogel connector) 430, connector elementals 432, insulatedenclosure 420, and ion conducting electrode lead 428.

FIGS. 5A-B show an embodiment of an electrode configuration 500 in whichtwo electrode contacts are housed within the same electrically insulatedenclosure 504. The electrodes 502A, 502B are in ionic contact with ionconducting materials 510/pads 512 that interface with the nerve tissue Nand/or area proximal to the nerve. Each electrode 502A, 502B is inelectrical communication via its own conductive lead 506 that is drivenby the current source 508. The internal electrodes 502A, 502B can bedriven cyclically with opposite current polarities to provide a constantnerve block. The current source 508 may be configured to be implantablewithin the body such that any leads 506 and electrodes 502A, 502B arealso fully contained within the body. Alternatively, the current source508 may be configured to remain outside the body and can be connectedvia wired or wireless connections in this or other embodiments.

In some embodiments, a system is configured for nerve block at specificnerves. One such nerve is the dorsal root, and/or dorsal root ganglion(DRG) through which pain signals pass (FIG. 6A). The associated dorsalroot ganglia from each vertebral level correspond to specific dermatomesin the body (FIG. 7), and blocking pain signals at the DRG level canreduce pain sensation at the innervated dermatome for that specific DRG.Access to the DRG may be facilitated by initial introduction of a needletip to the DRG. A stylet or obturator in the needle may be used toprevent occlusion of the opening or inadvertent tissue damage due totissue entrapment by the needle opening. The needle tip may beradiopaque as to be visualized under fluoroscopy or other radiographicmeans. Removal of the stylet from the needle may also occur in orderinject contrast agent to enable visualization of the local structuresand to confirm location of the needle tip. A short acting nerve blockagent may also be applied to confirm that the targeted DRG body whenblocked will provide adequate pain relief. Upon confirmation that theneedle is positioned properly and the DRG body is the appropriate targetfor nerve block, the stylet can be removed if not already removed, and ablocking electrode terminating in an EICCC with a single or multipleelectrode-nerve interface contacts can be introduced through the needle.As shown in FIG. 6C the DRG can be accessed with a needle 600, and theneedle 600 can be used to penetrate the dura mater as shown.Alternatively, the needle 600 may be positioned just outside the duramater without puncturing the tissue. The introduced electrode may haveradiopaque markers to enable visualization under fluoroscopy. Theintroduced electrode may also be encased within a secondary sheath thatprevents deployment of anchoring elements until the distal end of thesheath is retracted from the distal end of the introduced electrode toexpose tissue-anchoring elements. The enclosed electrode may also havestress-relief features such as coils or slack in the electrode body toaccommodate bodily motion that might dislodge the electrode without suchfeatures. As shown in FIG. 6D and FIG. 6E, the electrode-nerve interfacecontacts 604 can then be positioned in contact or proximal to the DRGand the introducing needle 600 can be retracted to leave the electrodelead 602 and nerve tissue interface 604 in the desired position. Theproximal end of the electrode may be connected to a current source tobegin nerve block and ensure proper electrode positioning. Once theappropriate positioning and block have been achieved, the optionalelectrode sheath can be retracted to expose retention mechanisms such asbarbs or frictional elements that prevent dislodging of the electrodefrom its desired position. Optionally, a conductive gel may be appliedbetween the electrode contact or contacts and nerve interface to furthermitigate loss of conduction block if the electrode contacts moverelative to the DRG body. In some embodiments, if after deployment ofthe retention mechanisms, placement must be adjusted, the sheath can beadvanced to retract the retention mechanisms and the electroderepositioned before redeploying the retention mechanisms. Once theelectrode is properly positioned, the electrode can be disconnected fromthe current source and the insertion needle removed over the electrodetoward its proximal end. The sheath can then be removed in a similarfashion. The current source can then be reconnected to the leadconnector to confirm proper placement and that no dislodging hasoccurred with insertion needle and sheath removal. After an optionalevaluative period, the current source may be implanted into the patientbody and the electrodes and/or leads may be replaced with permanentelectrodes for long-term implantation. The current source may furthercontain a battery or energy storage unit and electronic circuitry whichenables the unit to be programmable from a programming unit that cancommunicate with the implanted current source when in proximity to thebody site close to the current source implantation site. The currentsource energy source may be optionally rechargeable by the externalcommunication unit such as by inductive charging. FIG. 6B shows anembodiment of a blocking electrode 100 positioned along a DRG tofacilitate nerve block along with lead 112 and current source 114. It isunderstood that nerve block may include hypersuppression of the DRG.

In an alternative embodiment, the current source may be located outsidethe body of the patient permanently or temporarily to enable nerveblock. The electrodes may also be removed once deemed unnecessary thusprovided a temporary nerve block as desired. The nerve block may also beturned on and off periodically by modulating the current source asrequired to enable sensation during procedures that require patientfeedback for example.

Block of DRG at specific dermatomes can be used to localize therapeuticpain reduction due to neuralgias, angina, ischemic pain, and complexregional pain syndrome (CRPS). In the case of angina, cervical spinallevel nerve roots C6 and C7 have been implicated as frequently involvedwith the associated pain, and localized DRG block at one or both ofthese levels (with or without block of additional DRG at other levels)could be used to help manage this pain. (Nakajima et al., Cervicalangina: a seemingly still neglected symptom of cervical spine disorder?,Spinal Cord, 2006 44:509-513.) For example, complex regional painsyndrome (CRPS) is often localized to a single limb and generating alocalized block can provide more specific pain block for the source ofpain. For example, the lumbar dorsal root ganglia at levels L2, L3, L4have been shown to be able to reduce knee pain on the ipsilateral sideof the spine using conventional DRG stimulation techniques. (Bussel etal., Successful Treatment of Intractable Complex Regional Pain SyndromeType I of the Knee With Dorsal Root Ganglion Stimulation: A Case Report,Neuromodulation, 2015 Jan. 18(1):58-61) Ischemic pain frequently islocalized particularly for patients with poor extremity circulation andmay be similarly mitigated by targeting the appropriate DRG levels forblock.

As described above and illustrated in FIGS. 6A-6D and FIG. 7, an EICCCelectrode may be introduced in proximity to a DRG in order to blockand/or suppress the nerve tissue in the DRG to prevent distal painsignals from being registered by the individual. Furthermore, multipledorsal root ganglia may be targeted to generate unilateral and bilateralblocks or to adjust pain coverage based on pain presentation in thebody. EICCC electrodes may be placed at the target levels associatedwith the pain presentation and adjusted to tune the level of pain blockand coverage by adjusting the ionic current signal such as by tuning thecurrent amplitude at each DRG level targeted and in contact with anEICCC electrode. Localizing the pain block to specific regions of thebody can also help preserve normal sensory function in other regions ofthe body such that pain signals are not absent and can be used to signalan adverse situation and environmental conditions to the individual.

Compared to traditional SCS in which electrodes are placed along theposterior of the spinal cord in the epidural space, placement ofstimulating electrodes 800 in proximity to the lateral spinothalamictract (LT tract) (FIG. 8A) can leverage an EICCC to generate a nerveblock at the desired level (and/or spinal levels distal (away from thehead) to the EICCC since pain signals travel in the superior direction)and provide selective pain block depending on unilateral (left or right)or bilateral placement of electrodes 800. Electrode leads 802 may beplaced via a laminotomy (FIG. 8A middle, right) to enable access to theepidural space and then the electrodes leads 802 can be introduced andplaced into position along the lateral aspect or aspects of the spinalcolumn at the desired level or levels. Leads 802 may also be placedusing a percutaneous placement procedure with or without fluoroscopicguidance such as by using a Tuohy or similar needle 808 to introduce theelectrode lead 802 into the epidural space (FIG. 8B). The leads 802 canbe directed along the spinal column within the epidural space such thatthe lead 802 is between spinal nerve exit regions and the tissueinterface is in proximity to the lateral spinothalamic tract asillustrated in FIGS. 8C-8E. As seen in FIGS. 8C-8E, the electrode lead802 is positioned laterally to sit outside the lateral spinothalamictract such that the nerve tract can be blocked with the generated ioniccurrent from the electrode. Leads 802 may also be placed bilaterally tofacilitate bilateral block as each lateral spinothalamic tract carriespain information from the contralateral side of the body. The leads 802may then be connected to a current source to activate the nerve blockvia tissue interface 804 to ensure proper positioning and signal block.The lead 802 may then be disconnected from the current source and anoptional extension cable placed to connect the lead 802 to theimplantable current source. The current source may further contain abattery or energy storage unit and electronic circuitry which enablesthe unit to be programmable from a programming unit that can communicatewith the implanted current source when in proximity to the body siteclose to the current source implantation site. The current source energysource may be optionally wirelessly rechargeable by the externalcommunication unit such as by inductive charging.

In some embodiments multiple electrode leads such as illustrated in FIG.4D for example may be placed along the spinal cord, targeting thespinothalamic tract as shown in FIG. 8C. Furthermore, the electrodes maybe configured to have a multitude of tissue contacting regions whoseoutputs can be individually adjusted to optimize the nerve tissue block.An embodiment of an EICCC electrode is shown in FIGS. 10A-10C in whichmultiple tissue interfaces 404A, 404B are present on the electrode 402and are individually addressable. FIG. 10B is a close-up view of 10B-10Bof FIG. 10A. FIG. 10C is a close-up view of 10C-10C of FIG. 10A. In thisembodiment a dual system of EICCCs 400 are present and have parallellumens that are individually associated with each nerve tissue interfaceregion. In FIG. 10 the nerve tissue interface region and associatedEICCC are designated by matching letter labels, in this case A and B.Adjusting the current input and corresponding output at the distal endof the electrode can enable electric field shaping to facilitate desirednerve block while minimizing block of undesired structures. Analternative embodiment is captured in FIG. 5 in which individualelectrodes are also individually addressable and can be tuned to enabledesired block generation.

Using these methods of placement of blocking electrodes along the spinalcolumn to block the spinothalamic tract and the ability to tune theelectric field to generate nerve block and/or suppression, specifictargets for pain block can be facilitated. For example, trunk pain whichis moderated by the thoracic vertebral levels can be modulated byplacing leads along the thoracic spine while neck pain may be moderatedby providing block and/or suppression in the cervical spine. Upper limbpain may be moderated by providing a combination of cervical andthoracic level block and/or suppression while lower limb pain may bemoderated by a combination of lumbar and sacral level block and/orsuppression in the spine.

Generation of pain block can be used to facilitate peri-procedural painblock where motor control and non-pain sensations are desired. Forexample in labor and delivery of a child, one of the challenges withpain management particularly with epidural anesthesia is the reductionin ability to be sensate in the lower body. Due to the non-specificnature of the delivered anesthesia in the epidural space sensory, pain,and motor neurons are impacted. The epidural anesthesia can lead todifficulty with generating pushing force during the birthing process andcan lead to numbness a few hours after birth impairing motor abilitiessuch as the ability to walk. In some instances, epidurals are furtherimplicated in fetal and newborn health including breastfeedingdifficulty. Using the blocking electrodes described above to target thespinothalamic tract and/or dorsal root ganglia, the undesired pain canbe targeted without generating the side effects (or reducing sideeffects) associated with current epidural anesthesia techniques becauseonly the pain tracts are targeted and not any other motor or sensorytracts. Furthermore, in the case in which ionic current is delivered tothe nerve tissue in a reversible blocking fashion, the stopping of blockcan enable the patient to immediately be restored to normal painsensation if desired and any off-target block can be reversed enablingimmediate body function restoration.

Beyond central nervous system interventions, a safe direct current blockcan also be facilitated in the peripheral nervous system in which EICCCelectrodes are placed in contact or in proximity to peripheral nerves tofacilitate block. Specific pain targets include focal pain, phantom limbpain, neuroma pain, and neuralgias. Targeting the peripheral nervesproximally (i.e. closer to the spinal cord) from the site of pain forblock can suppress pain from the distal site. Specific to neuralgias,postherpetic neuralgia (after shingles) can be targeted based on thepresentation of the outbreak which will trace specific dermatomes. Fortrigeminal neuralgia, the trigeminal nerve (and/or trigeminal ganglionand/or trigeminal nucleus in the brainstem) can be targeted for block toreduce pain that commonly manifests as facial pain. Another target isthe glossopharyngeal nerve which produces pain in the neck and throat.Neuralgia in extremities such as the hands, arms, feet, and legs asfrequently caused due to diabetes-related neuropathies are alsopotential targets.

Outside of pain reduction, nerve block and activity suppression can beused to improve cardiovascular health in specific targeted ways.Hypertension which is implicated as a leading cause of cardiovasculardisease has been found to be able to be moderated by modulation of therenal nerves to reduce activation of the sympathetic nervous system.Current techniques exist to denervate or ablate these nerves using avariety of energy sources such as ultrasound and radiofrequency energy.(Krum et al., Catheter-based renal sympathetic denervation for resistanthypertension: a multicentre safety and proof-of-principle cohort study.The Lancet. 2009 373(9671):1275-1281. US Patent Application:2012/0016226) Using the tools described herein, selective nerve blockcan be used to facilitate activity reduction in the renal nerves andsympathetic nervous systems to facilitate reduction in hypertension. Asshown in FIG. 1I, the blocking electrode leads 1100A, 1100B contact therenal nerves to facilitate a block or suppression Also systematicallyillustrated is EICCC 1104 openly connected at 1106 to current source(not shown). The contact may also be configured in a cuff format tosurround the renal artery and provide a circumferential direct currentto the outer perimeter of the renal artery and block the nerve tissuesurrounding the artery. The delivered blocking current can also beadjusted to fit the individual physiological response to sympatheticnerve block which cannot be done currently with destructive methods suchas ablation.

Heart failure is another target disease state with known associationwith upregulation of the sympathetic nervous system. By using a blockingelectrode to moderate the sympathetic ganglia, particularly reducingactivity of the cervical sympathetic ganglia, excessive heart activitycan be reduced to mitigate overworking of the heart. Similar to dorsalroot ganglion access, the cervical ganglia may be accessed for block. Asshown in FIG. 12, the relevant sympathetic ganglia including thecervical and stellate (cervicothoracic) ganglia are shown along withtheir innervation targets in the heart. Methods of access includeposterior access as well as through the pleural cavity.

Tachycardia or other tachyarrhythmias such as atrial fibrillation,atrial flutter, multifocal atrial tachycardia, paroxysmalsupraventricular tachycardia, ventricular tachycardia, and ventricularfibrillation for example may also be regulated by modulation of thesympathetic nervous system and can be influenced toward a more normalstate by targeting the cervical sympathetic ganglia (FIG. 13) to providea block of the sympathetic ganglia. Methods of access include posterioraccess as well as through the pleural cavity.

Modulation of the parasympathetic innervation of the heart can be usedto regulate cardiac function. Stimulation of the vagus nerve is known tolead to bradycardia, or bradycardia, and suppression of heart rate.Conversely, by creating a vagal nerve block, the heart rate suppressingneural signaling can be reduced or shut down leading to increase inheart rate by reducing the vagal nerve signal. Particularly, the rightvagal nerve which innervates the sinoatrial node to help regulate heartrate can be blocked or suppressed to enable increase in heart rate. Asseen in FIG. 14, an EICCC electrode 1400 can be placed around or inproximity to the right (and/or left) vagus nerve within the right sideof the neck and/or chest with an electrode lead 1402 running down towardan implantable current source 1404 shown in the right pectoral region.The electrode lead 1402 may be placed in the right subclavian region orother desired location and tunneled below the skin to the currentsource.

In addition to cardiovascular function, the nervous system plays asignificant role in regulating gastric processes including satiety (lackof hunger) and satiation (fullness). The vagus nerves innervate thestomach with the majority of signals to the brain reporting state ofsatiety and satiation. Using the EICCC electrode 1600, a block or nervesuppression of the vagus nerves can be generated to give the individuala heightened sense of satiety and satiation. Gastrointestinal nerves canalso be modulated to either increase or decrease GI transit time. Asseen in FIGS. 15-16, an exemplary dual EICCC system is shown in whicheach vagus nerve is wrapped in a cuff-format tissue interface 1606 atwhich ionic current is deposited at the tissue site from the EICCCs 1600which are connected via electrode leads 1602 as well as to the currentsource 1604. The tissue interface may be moderated by a porous frit orother ionically conductive medium such as a conductive hydrogel aspreviously described herein. FIG. 16 is a close-up view of FIG. 15 nearthe gastro-esophageal junction region.

Sympathetic nerve suppression or block can also be used to regulatehepatic, gallbladder, and/or pancreatic function and influence glucoseand insulin production as shown in FIG. 17. Suppressing or blocking thehepatic nerves can lead to increase insulin production and reduceresistance to insulin enabling management of adult onset or type 2diabetes in which insulin production is reduced or resistance to insulinfunction is increased. Using the EICCC electrode 1800, a block or nervesuppression of the hepatic nerves can be generated to increase insulinproduction and reduce insulin resistance. As seen in FIG. 18, an EICCCsystem is shown in which the nerves around the hepatic artery and theartery are surrounded by a cuff-format tissue interface 1806 at whichionic current is deposited at the tissue site from the EICCC 1800connected via an electrode lead 1802 as well as to the current source1804. The tissue interface 1806 may be moderated by a porous frit orother ionically conductive medium such as a conductive hydrogel aspreviously described herein. In other embodiments, splenicneuromodulation could either improve depressed immune function, orreduce inflammation or hyperimmune function (e.g., in autoimmuneconditions such as SLE, rheumatoid arthritis, Crohn's, ulcerativecolitis), or other conditions.

Movement disorders including Tourette's syndrome, dystonia, Parkinson'sdisease (and associated rigidity), essential tremor, spasticity, andepilepsy can also be influenced by moderating neural tissue activity.These disorders and diseases are characterized by neural hyperactivityin specific parts of the brain, which can lead to the symptomaticpresentation. Targeting specific regions of the brain for blockincluding those captured in Table 1 below can be used to help manage apatient's symptoms. It is recognized that blocking of these targetscould be either unilateral or bilateral.

TABLE 1 Movement disorders and brain region targets for nerve tissueblock for symptom reduction. Disease, Disorder Region of the BrainTourette's 1. anteromedial globus pallidus syndrome 2. Ventral anteriorthalamus 3. Ventrolateral motor part of thalamus Dystonia 1. Internalsegment of the globus pallidus (GPi) Parkinson's 1. Internal segment ofthe globus pallidus (GPi) disease 2. Subthalamic nucleus (STN), 3.Pedunculopontine nucleus (PPN), 4. Vim (ventro-intermediate nucleus) (asubdivision of the thalamus) Essential 1. Thalamus (Vim:ventro-intermediate nucleaus) Tremor 2. posterior subthalamic area (PSA)Epilepsy 1. Anterior nucleus of the thalamus 2. Other identifiedepileptogenic foci

Similarly, psychiatric disorders including treatment resistantdepression (TRD), anxiety, obsessive compulsive disorder (OCD), andpost-traumatic stress disorder (PTSD) have are targets for neural blockto reduce symptoms from these conditions. Targeting specific regions ofthe brain for block including those captured in the Table 2 below can beused to help manage a patient's symptoms. It is recognized that blockingof these targets could be either unilateral or bilateral. Otherdisorders that can be treated can include, for example, schizophrenia,schizoaffective disorder, bipolar disorder, mania, alcoholism, substanceabuse, and others.

TABLE 2 Psychiatric disorders and brain region targets for nerve blockfor symptom reduction. Disease, Disorder Region of the BrainTreatment 1. Subgenual cingulate cortex, Resistant 2. Inferior thalamicpeduncle, and Depression 3. Nucleus accumbens Anxiety 1. Nucleusaccumbens OCD 1. Ventral internal capsule 2. Ventral striatum PTSD 1.Basolateral amygdala

Chronic pain is another target in which specific regions in the brainhave been implicated in affecting chronic pain. One such region is thethalamus which is the entry point for pain signaling to the brain.Specific regions in the thalamus have been identified as targets forneural activity reduction to reduce chronic pain as shown in Table 3below. It is recognized that blocking of these targets could be eitherunilateral or bilateral

TABLE 3 Brain region targets for nerve block for pain reduction.Disease, Disorder Region of the Brain Chronic pain 1. Ventromedialthalamic nuclei 2. Intralaminar thalamic nuclei

In some embodiments a system is configured for generation of nerve blockfor disorders and diseases that can be addressed by reducing neuralactivity in specific regions of the brain responsible for the specificdisorder. Neural activity reduction can be facilitated by directlyblocking and reducing activity of specific neurons as well as byblocking pathways along which excessive neural signaling is occurring.In some embodiments, this system for deep brain block (DBB) comprisesall or some of the steps of identification of the anatomic target sitefor block, creating an access site to the exterior of the brain tissue,creating a path through the brain tissue to the target site, evaluatingthe suitability of the target site for block, adjusting or refining thelocation of the target site, providing nerve block at the target site,and adjusting the nerve tissue block strength or location. Practically,this process may be implemented using techniques known in the field ofdeep brain stimulation (DBS) in which a target anatomic site isidentified using a combination of imaging techniques such as but notlimited to magnetic resonance imaging (MRI) including functional MRI(fMRI), computed tomography (CT), PET scanning, and/or x-rays. This sitecan then be accessed using stereotactic techniques to register anidentified region from imaging to the physical anatomy on the patient. Aframe may be fixed to the patient's head and skull to allow for spatialregistration during the procedure. An access site to the brain tissue inthe form of a burr hole or craniotomy can be formed with or withoutadditional access tools fixed to the skull such as insertion cannula andadvancement/retraction equipment to access the target site. Advancementof a nerve tissue activity measurement probe through the brain tissue tothe target site may be used to enable evaluation of the suitability ofthe brain region. This probe may record neural activity to determinethat the measured signals are consistent with that of tissue requiringblock. If the signal characteristics indicate that the location is notoptimal or appropriate for block, the probe may be adjusted until thecorrect location is identified. The measurement probe may be exchangedwith the blocking electrode which can then be inserted with the activeportion of the electrode positioned within the target site. Activationof the blocking signal can then be used to assess efficacy of the blockas well as to tune the strength of the signal. The blocking electrodecan then be fixed to the skull to maintain the active portion's (e.g.,region delivering ionic current) position at the target site. Anextension lead can be connected to the affixed blocking electrode andconnected to an implantable current source, similar to an implantablepulse generator (IPG), whose output signal can be adjusted to facilitateoptimal symptom reduction. Blocking electrodes may be implantedunilaterally or bilaterally as the contralateral side of the body isaffected by specific anatomic target sites.

FIG. 9A shows an electron-ion current conversion cell (EICCC) electrode900 configured to interface with a deep brain block (DBB) target in thethalamus. The nerve tissue interface 904 contacts and provides block tothe target site in the thalamus while an electrode lead 902 provides aconduit between the thalamus and the exterior of the skull. An extensionport in the skull anchor 910 allows for communication between thecurrent source 908 and the electrode lead 902 via an electrode extension906 which can connect electrically with the port and current source 908.Within the lead 902 itself the EICCC blocking electrode comprises aninternal electrode 916 such as an Ag/AgCl wire which converts electroncurrent to ionic current in an ion conductive medium 918 such as salineand generates ionic current at the nerve tissue interface 904 via anionically conductive material such as a porous frit 920 designed toallow ions to flow through it to generate a block at the nerve tissuesite. The ionically conductive medium 918 and/or tissue interfacematerial may also comprise a hydrogel or other ionically conductivematerial as described elsewhere herein.

Specific to epilepsy, electrocorticography (ECoG) may be performed toidentify the epileptic focus or foci for targeting of electrodeplacement and nerve block in that location. The implanted blockingelectrode may be used to block or suppress nerve tissue activity ondemand by the user during an epileptic fit or when sensing the onset ofan epileptic fit. Moreover, the system including the blocking electrodemay be configured to alternatively lower the field potential of acluster of neurons prone to causing epileptic fits such that epilepticfits may be prevented instead of being reacted to when they are about tooccur or when they are occurring. In another embodiment, the blockingelectrode is combined with a measurement or sensing electrode such thatthe activity of the neuron cluster or clusters comprising the epilepticfocus or foci are monitoring and when activity indicative of onset of anepileptic episode is measured, the system can automatically generates ablock to reduce activity of the target cells in a closed-loop fashion.In FIG. 9B an embodiment of a blocking/suppressing electrode 950 with anintegrated sensing electrode 922 is shown in which a sensing electrode922 is in proximity to the nerve tissue interface 904 such that sensingof the target neuron activity can occur and the signal from the sensingelectrode 922 feeds back to the current source 908 which can beactivated based on the sensing electrode signal to generate an ioniccurrent at the nerve tissue 904 interface to disrupt or prevent onset ofan epileptic fit. The sensing electrode 922 can include an insulatedconductive path to electrode extension 924. In other embodiments, theblocking electrode may also serve as the sensing electrode 922 (e.g.when blocking current is not being applied). An electrode for blockingtissue to treat epilepsy may be configured as straight probe which isimplanted deeper than the cortical surface, or may be configured as aepi-cortical electrode (e.g., by having a planar or conformal element).

The systems and methods described in the figures above may be used togenerate DC nerve block. Depending on the specific direct currentapplication of nerve block, nerve suppression, or continued block afterremoval or stopping of the current may occur, and hypersuppression mayresult for continued nerve blockade in excess of one minute afterremoval of the DC source to delay nerve conduction recovery. The nerveblock and suppression may be generated in an intermittent or continuousmanner depending on the desired application. Means for continuous nerveblock have been described that provide for safe delivery of nerve blockvia ionic current utilizing multiple electrodes or sequenced electrodecontact activation enabling a means to modulate nerve conduction safelywithout necessitating complex mechanical systems. The system may befully or partially implantable, or completely non-implantable (e.g.,transcutaneous) with all tissue contacting materials biocompatible fortissue contact and implantation compatibility.

Various other modifications, adaptations, and alternative designs are ofcourse possible in light of the above teachings. Therefore, it should beunderstood at this time that within the scope of the appended claims theinvention may be practiced otherwise than as specifically describedherein. It is contemplated that various combinations or subcombinationsof the specific features and aspects of the embodiments disclosed abovemay be made and still fall within one or more of the inventions.Further, the disclosure herein of any particular feature, aspect,method, property, characteristic, quality, attribute, element, or thelike in connection with an embodiment can be used in all otherembodiments set forth herein. Accordingly, it should be understood thatvarious features and aspects of the disclosed embodiments can becombined with or substituted for one another in order to form varyingmodes of the disclosed inventions. Thus, it is intended that the scopeof the present inventions herein disclosed should not be limited by theparticular disclosed embodiments described above. Moreover, while theinvention is susceptible to various modifications, and alternativeforms, specific examples thereof have been shown in the drawings and areherein described in detail. It should be understood, however, that theinvention is not to be limited to the particular forms or methodsdisclosed, but to the contrary, the invention is to cover allmodifications, equivalents, and alternatives falling within the spiritand scope of the various embodiments described and the appended claims.Any methods disclosed herein need not be performed in the order recited.The methods disclosed herein include certain actions taken by apractitioner; however, they can also include any third-party instructionof those actions, either expressly or by implication. For example,actions such as “applying direct current to a nerve” includes“instructing the applying of direct current to a nerve.” The rangesdisclosed herein also encompass any and all overlap, sub-ranges, andcombinations thereof. Language such as “up to,” “at least,” “greaterthan,” “less than,” “between,” and the like includes the number recited.Numbers preceded by a term such as “approximately”, “about”, and“substantially” as used herein include the recited numbers (e.g., about10%=10%), and also represent an amount close to the stated amount thatstill performs a desired function or achieves a desired result. Forexample, the terms “approximately”, “about”, and “substantially” mayrefer to an amount that is within less than 10% of, within less than 5%of, within less than 1% of, within less than 0.1% of, and within lessthan 0.01% of the stated amount.

What is claimed is:
 1. A system for nerve block of a patient utilizing acapacitive chargeable electrode, comprising: a current generator; atleast one implantable electrode comprising titanium nitride or tantalum,the at least one electrode configured to be in electrical communicationwith the current generator; a controller configured to signal thecurrent generator to: generate a first current with a first polarityproximal to the at least one electrode sufficient to at least partiallyblock conduction in a nerve, wherein an amount of charge in the at leastone electrode is configured to decrease and generate current in an ioniccomponent proximate the at least one electrode when the electrode isimplanted within the patient; and generate a second current with asecond polarity proximal to the at least one electrode sufficient toincrease the amount of charge in the at least one electrode, and asensor configured to determine the state of stored charge of the atleast one electrode, and wherein the controller is further configured toreceive data from the sensor and discontinue at least one of the firstcurrent signal or the second current signal when an amount of water isbeing electrolyzed.
 2. The system of claim 1, wherein the at least oneelectrode is housed in an insulated enclosure.
 3. The system of claim 1,wherein the system is devoid of any mechanically moving parts.
 4. Thesystem of claim 1, wherein the at least one implantable electrodecomprises high surface area to volume structures.
 5. The system of claim4, wherein the high surface area to volume structures are selected fromthe group consisting of: roughened surfaces, woven surfaces, patternedsurfaces, reticulated foam structures, porous sintered bead structures,and nano- or micro-patterned structures.
 6. The system of claim 4,wherein the high surface area to volume structures comprise roughenedsurfaces.
 7. The system of claim 4, wherein the high surface area tovolume structures comprise micro-patterned structures.
 8. The system ofclaim 4, wherein the high surface area to volume structures comprisenano-patterned structures.
 9. The system of claim 1, wherein the sensorcomprises a reference electrode.
 10. The system of claim 1, wherein thesensor is configured to measure voltage or potential at the at least oneimplantable electrode.
 11. A system for nerve block of a patientutilizing a capacitive chargeable electrode, comprising: a currentgenerator; at least one implantable electrode comprising a high chargecarrying capacity material configured to be spaced apart from a nerveinterface by an ionic component, the at least one implantable electrodeconfigured to be in electrical communication with the current generator;a controller configured to signal the current generator to: generate afirst current with a first polarity proximal to the at least oneimplantable electrode sufficient to at least partially block conductionin a nerve, wherein an amount of stored charge in the at least oneelectrode is configured to decrease and generate current in an ioniccomponent proximate the at least one electrode when the electrode isimplanted within the patient; and generate a second current with asecond polarity proximal to the at least one implantable electrodesufficient to increase the amount of stored charge of the at least oneimplantable electrode; and a sensor configured to determine the state ofcharge of the at least one implantable electrode, wherein the controlleris further configured to receive data from the sensor and discontinue atleast one of the first current or the second current when an amount ofwater is being electrolyzed.
 12. The system of claim 11, wherein thesystem is devoid of any mechanically moving parts.
 13. The system ofclaim 11, wherein the at least one implantable electrode is at leastpartially surrounded by an electrolyte solution.
 14. The system of claim11, wherein the high charge carrying capacity material comprisestitanium nitride.
 15. The system of claim 11, wherein the controller isconfigured to maintain the nerve in a hypersuppressed state at leastpartially preventing conduction of the nerve for at least about 10minutes after cessation of delivering of the first current.
 16. A methodfor nerve block of a patient utilizing a chargeable electrode,comprising: generating a first current of a first polarity through atitanium nitride or tantalum implanted electrode proximate a nervesufficient to at least partially block conduction in the nerve, whereinthe electrode generates current in an ionic component proximate the atleast one electrode sufficient to create at least a partial block in thenerve and decrease the amount of stored charge in the implantedelectrode; generating a second current of a second polarity opposite thefirst polarity through the implanted electrode; dynamically sensing theamount of the stored charge in the implanted electrode while deliveringthe first current; and ceasing delivery of the first current when theamount of the stored charge is sensed to reach a pre-determinedthreshold value; and discontinuing at least one of the first currentsignal or the second current signal when an amount of water is beingelectrolyzed, wherein the second current increases the amount of thestored charge of the implanted electrode to recharge the implantedelectrode.
 17. The method of claim 16, wherein the amount of water isbeing electrolyzed is a predetermined threshold amount of water.
 18. Themethod of claim 16, wherein the implanted electrode comprises highsurface area to volume structures.
 19. The method of claim 18, whereinthe high surface area to volume structures are selected from the groupconsisting of: roughened surfaces, woven surfaces, patterned surfaces,reticulated foam structures, porous sintered bead structures, and nano-or micro-patterned structures.
 20. The method of claim 18, wherein thehigh surface area to volume structures are selected from the groupconsisting of: roughened surfaces, woven surfaces, patterned surfaces,reticulated foam structures, porous sintered bead structures, and nano-or micro-patterned structures.
 21. A system for nerve block of a patientutilizing a capacitive chargeable electrode, comprising: a currentgenerator; at least one implantable electrode comprising titaniumnitride or tantalum, the at least one electrode configured to be inelectrical communication with the current generator; a controllerconfigured to signal the current generator to: generate a first currentwith a first polarity proximal to the at least one electrode sufficientto at least partially block conduction in a nerve, wherein an amount ofcharge in the at least one electrode decreases and generates current inan ionic component proximate the at least one electrode when theelectrode is implanted within the patient; and generate a second currentwith a second polarity proximal to the at least one electrode sufficientto increase the amount of charge in the at least one electrode, whereinthe at least one electrode is housed in an insulated enclosure.
 22. Asystem for nerve block of a patient utilizing a capacitive chargeableelectrode, comprising: a current generator; at least one implantableelectrode comprising a high charge carrying capacity material configuredto be spaced apart from a nerve interface by an ionic component, the atleast one implantable electrode configured to be in electricalcommunication with the current generator; and a controller configured tosignal the current generator to: generate a first current with a firstpolarity proximal to the at least one implantable electrode sufficientto at least partially block conduction in a nerve, wherein an amount ofstored charge in the at least one electrode is configured to decreaseand generate current in an ionic component proximate the at least oneelectrode when the electrode is implanted within the patient; andgenerate a second current with a second polarity proximal to the atleast one implantable electrode sufficient to increase the amount ofstored charge of the at least one implantable electrode, wherein thecontroller is configured to maintain the nerve in a hypersuppressedstate at least partially preventing conduction of the nerve for at leastabout 10 minutes after cessation of delivering of the first current. 23.A system for nerve block of a patient utilizing a capacitive chargeableelectrode, comprising: a current generator; at least one implantableelectrode comprising a high charge carrying capacity material configuredto be spaced apart from a nerve interface by an ionic component, the atleast one implantable electrode configured to be in electricalcommunication with the current generator; a controller configured tosignal the current generator to: generate a first current with a firstpolarity proximal to the at least one implantable electrode sufficientto at least partially block conduction in a nerve, wherein an amount ofstored charge in the at least one electrode is configured to decreaseand generate current in an ionic component proximate the at least oneelectrode when the electrode is implanted within the patient; generate asecond current with a second polarity proximal to the at least oneimplantable electrode sufficient to increase the amount of stored chargeof the at least one implantable electrode; receive data relating to thestate of charge of the at least one implantable electrode; and receivedata regarding when an amount of water is being electrolyzed, anddiscontinue at least one of the first current or the second current whena predetermined threshold amount of water is being electrolyzed.
 24. Asystem for nerve block of a patient utilizing a capacitive chargeableelectrode, comprising: a current generator; at least one implantableelectrode comprising a high charge carrying capacity material, the atleast one implantable electrode configured to be in electricalcommunication with the current generator; a controller configured tosignal the current generator to: generate a first current with a firstpolarity proximal to the at least one implantable electrode sufficientto at least partially block conduction in a nerve, wherein an amount ofstored charge in the at least one electrode is configured to decreaseand generate current proximate the at least one electrode when theelectrode is implanted within the patient; generate a second currentwith a second polarity proximal to the at least one implantableelectrode sufficient to increase the amount of stored charge of the atleast one implantable electrode; receive data relating to the state ofcharge of the at least one implantable electrode; and receive dataregarding when an amount of water is being electrolyzed, and discontinueat least one of the first current or the second current when apredetermined threshold amount of water is being electrolyzed.
 25. Thesystem of claim 24, wherein the high charge carrying capacity materialcomprises titanium nitride or tantalum.
 26. A system for alleviatingpain of a patient utilizing a capacitive chargeable electrode,comprising: a current generator; at least one implantable electrodecomprising titanium nitride or tantalum, the at least one electrodeconfigured to be in electrical communication with the current generator;a controller configured to signal the current generator to: generate afirst current with a first polarity proximal to the at least oneelectrode sufficient to at least modulate conduction in a nerve, whereinan amount of charge in the at least one electrode is configured todecrease and generate current in an ionic component proximate the atleast one electrode when the electrode is implanted within the patient;and generate a second current with a second polarity proximal to the atleast one electrode sufficient to increase the amount of charge in theat least one electrode, and a sensor configured to determine the stateof stored charge of the at least one electrode, and wherein thecontroller is further configured to receive data from the sensor anddiscontinue at least one of the first current signal or the secondcurrent signal when an amount of water is being electrolyzed.
 27. Thesystem of claim 26, wherein the at least one electrode is housed in aninsulated enclosure.
 28. The system of claim 26, wherein the system isdevoid of any mechanically moving parts.
 29. The system of claim 26,wherein the at least one implantable electrode comprises high surfacearea to volume structures.
 30. The system of claim 28, wherein the highsurface area to volume structures are selected from the group consistingof: roughened surfaces, woven surfaces, patterned surfaces, reticulatedfoam structures, porous sintered bead structures, and nano- ormicro-patterned structures.
 31. The system of claim 28, wherein the highsurface area to volume structures comprise roughened surfaces.
 32. Thesystem of claim 28, wherein the high surface area to volume structurescomprise micro-patterned structures.
 33. The system of claim 28, whereinthe high surface area to volume structures comprise nano-patternedstructures.
 34. A system for treating pain of a patient utilizing acapacitive chargeable electrode, comprising: a current generator; atleast one implantable electrode comprising a high charge carryingcapacity material configured to be spaced apart from a nerve interfaceby an ionic component, the at least one implantable electrode configuredto be in electrical communication with the current generator; acontroller configured to signal the current generator to: generate afirst current with a first polarity proximal to the at least oneimplantable electrode sufficient to modulate conduction in a nerve,wherein an amount of stored charge in the at least one electrode isconfigured to decrease and generate current in an ionic componentproximate the at least one electrode when the electrode is implantedwithin the patient; and generate a second current with a second polarityproximal to the at least one implantable electrode sufficient toincrease the amount of stored charge of the at least one implantableelectrode; and a sensor configured to determine the state of charge ofthe at least one implantable electrode, wherein the controller isfurther configured to receive data from the sensor and discontinue atleast one of the first current or the second current when an amount ofwater is being electrolyzed.
 35. The system of claim 34, wherein thesystem is devoid of any mechanically moving parts.
 36. The system ofclaim 34, wherein the at least one implantable electrode is at leastpartially surrounded by an electrolyte solution.
 37. The system of claim34, wherein the high charge carrying capacity material comprisestitanium nitride.
 38. The system of claim 34, wherein the controller isconfigured to maintain the nerve in a hypersuppressed state at leastpartially preventing conduction of the nerve for at least about 10minutes after cessation of delivering of the first current.
 39. A methodfor treating pain of a patient utilizing a chargeable electrode,comprising: generating a first current of a first polarity through atitanium nitride or tantalum implanted electrode proximate a nervesufficient to modulate conduction in the nerve, wherein the electrodegenerates current in an ionic component proximate the at least oneelectrode sufficient to alleviate pain in the patient and decrease theamount of stored charge in the implanted electrode; generating a secondcurrent of a second polarity opposite the first polarity through theimplanted electrode; dynamically sensing the amount of the stored chargein the implanted electrode while delivering the first current; andceasing delivery of the first current when the amount of the storedcharge is sensed to reach a pre-determined threshold value; anddiscontinuing at least one of the first current signal or the secondcurrent signal when an amount of water is being electrolyzed, whereinthe second current increases the amount of the stored charge of theimplanted electrode to recharge the implanted electrode.
 40. The methodof claim 39, wherein the amount of water is being electrolyzed is apredetermined threshold amount of water.
 41. The method of claim 39,wherein the implanted electrode comprises high surface area to volumestructures.